Method and apparatus for determining local acoustic field intensity within a soft solid

Abstract

This method, for determining the local intensity (I0) of an acoustic field propagating in a target region of a soft solid, at a position located within said target region, includes at least the following steps: determining (102) a value of an ultrasound attenuation coefficient (α) of the soft body in the target region; determining (104) a value of the shear modulus (μ) of the soft body in the target region; determining (106) a value of the speed of sound (c) in the target region of the soft body; and building (110), with the values determined in steps a), b) and c), a viscoelastic model (M) of a steady-state displacement induced by an acoustic field having a time invariant shape or a viscoelastic model of a difference between two steady-state displacements induced by an acoustic field having a time invariant shape. Moreover, this method also includes the following steps: applying (112) to the target region the acoustic field emitted by an ultrasound source, for a duration such that the acoustic field induces a steady-state localized deformation (Formula (I)) of the soft body in the target region; measuring (114) at least one steady state displacement induced by the acoustic field at a given position in the target region; and computing (116) the amplitude of the intensity of the acoustic field at said given position by inverting the viscoelastic model (M) at said given position, for the displacement(s) measured at step f).

Description

TECHNICAL FIELD OF THE INVENTION

This invention relates to a method for determining, at any arbitrary location within a target region of a soft solid, a local intensity of an acoustic field propagating in this target region. This invention also relates to an apparatus for implementing such a method.

In the meaning of the present invention, a soft solid is an organic tissue which can have an animal or vegetal origin. For instance, such a soft solid can be an organ of a human or animal body, or a part of a vegetable. A soft solid can also be a food element, e.g. cheese, a cosmetic compound, or a non-metallic part of an equipment such as prosthesis, this non-metallic part being made of a natural or synthetic material.

BACKGROUND OF THE INVENTION

When an acoustic field propagates in a soft solid, in order to measure a physical parameter of this solid or in order to apply a treatment, it is essential that the spatial distribution of the acoustic field in the soft solid is precisely controlled, in particular in order not to damage the soft solid, e.g. by overheating.

For instance, diagnostic and therapeutic ultrasound applications rely on delivering a specific intensity distribution of an acoustic field over a given duration. In medical applications, the ultrasound beam may be unexpectedly attenuated, or deflected, or both, because of tissue heterogeneity. Ideally, beam alteration should be detected and corrected. But, as of today, there is no way to measure intensity in biological tissues. Beam alteration is therefore likely to go unnoticed, with potential consequences on safety and efficacy of the diagnostic and/or of the treatment.

The intensity distribution of an acoustic field in a region of interest can be estimated using an inverse problem approach. Specifically, in a first iteration, some initial guess of the intensity distribution is entered in the simulation. The difference between the field predicted from simulation and a field measured experimentally is calculated. In subsequent iterations, the intensity distribution entered in the simulation is varied and the difference between the field predicted from simulation and the field measured experimentally is minimized iteratively. An algorithm selects the intensity distribution that minimizes the discrepancy between simulations and experiment. However, the chosen solution may correspond to a local minimum. It may therefore be inaccurate. This approach may therefore be unreliable.

Using a viscoelastic model is known in the field of ultrasound imaging, as explained by Bercoff et al. in “The role of viscosity in the impulse diffraction field of elastic waves induced by the acoustic radiation force” (IEEE Transactions on Ultrasonics, Ferroelectrics, and Frequency Control, Vol. 51, No. 11, November 2004). This document focuses on the determination of soft tissue elasticity and is not concerned with the actual intensity of an acoustic field applied for an experiment.

In “Monitored steady-state excitation and recovery (MSSER) radiation force imaging using viscoelastic models” (IEEE Transactions on Ultrasonics, Ferroelectrics, and Frequency Control, Vol. 55, No. 7, July 2008) and in US-A-20100138163, Mauldin et at consider a steady-state situation for measuring an elasticity. Here again, this does not allow monitoring the intensity of an acoustic field used in an experiment.

US-A-2012/226158 discloses a system and a method for correcting errors in shear wave measurements. This method disclosed does not allow for the measurement of an acoustic intensity. This method is therefore fundamentally different from the method described below.

Usually, the power of the beam of the acoustic field in the target region, which depends on the ultra-sound beam distribution, is estimated by simulation. This simulation is based on a situation in a homogenous medium, such as water. This can be satisfactory when the soft solid is also homogeneous.

In practice, many soft solids, in particular biological tissues, are heterogeneous. They can include localized variations, such as tumors and/or fat with a distribution which depends, amongst others, on the size of the organism to be studied, for instance a patient. Thus, in real life applications of ultrasonic beams, the beam can be deflected, attenuated or dilated/diverging due to heterogeneities, so that the practitioner does not know how effective the diagnostic or the treatment is and for how long is should be applied.

In other words, the intensity of the ultrasonic field in the target region of the diagnostic and/or of the treatment is not controlled. One relies on the simulation made in water, which is not appropriate for the soft solid.

The same problem occurs when an acoustic field is used for non-medical purposes, e.g. for quality control in the food, cosmetic or mechanical industry, where heterogeneities may result from holes or fat in a sample.

SUMMARY OF THE INVENTION

The invention aims at solving these problems by proposing an improved method which actually allows determining a local intensity of an acoustic field propagating in a target region of a soft solid, thus allows controlling that such an acoustic field is being efficiently used.

To this end, the invention concerns a method for determining a local intensity of an acoustic field induced by an ultrasound source and propagating in a target region of a soft solid, at a position located within said target region, characterized in that said method includes at least the following steps:

• • a) determining a value of an ultrasound attenuation coefficient of the soft solid in the target region;
  • b) determining a value of the shear modulus of the soft solid in the target region;
  • c) determining a value of the speed of sound in the target region of the soft solid;
  • d) building, with the values determined in steps a), b) and c), a viscoelastic model of a steady-state displacement induced by an acoustic field having a time invariant shape, or a viscoelastic model of a difference between two steady-state displacements induced by an acoustic field having a time invariant shape;
  • e) applying, to the target region, the acoustic field emitted by an ultrasound source, for a duration such that the acoustic field induces a steady-state localized deformation of the soft solid in the target region;
  • f) measuring at least one steady-state displacement, or a steady-state displacement difference, induced by the acoustic field at a given position in the target region; and
  • g) computing the amplitude of the intensity of the acoustic field at said given position by inverting the viscoelastic model at said given position, for the displacement(s) measured at step f).

In the meaning of the invention, “steady-state” means that the displacement or displacement difference measured at step d) is obtained in a steady-state steady state condition, in other words that it is invariant in time during the implementation of the method of the invention.

The building of the viscoelastic model can be performed with a Green's function or with any other suitable tool, such as the finite differences method, or using the finite elements method, as described by Eskandari et al. in “Viscoelastic characterization of soft tissue from dynamic finite element models” (Physics in medicine and biology 2008; 53(22): 6569-90).

In physics, an inverse problem is the process of determining the causes of a phenomenon, based on the observation of its effects. For simple phenomena, the solution can be as simple as solving an equation. On the other hand, complex phenomena require extensive numerical calculations performed using a computer or an array of computers. Methods for solving inverse problems are described in the book “Parameter Estimation and Inverse Problems”, (2018), Third Edition, Elsevier. ISBN 9780128134238, ISBN 9780128134238″ by Aster Richard; Borchers Brian, and Thurber Clifford. In the present invention, inversion of the viscoelastic model can be achieved using any of the known methods described in this book.

Thanks to the invention, it is possible to determine how efficient an acoustic beam is, in particular to take into account a possible alteration of the acoustic field, such as a deflection or a diverging configuration of the beam. When detected, such an alteration can be corrected, which improves the efficiency of the control or treatment performed with the acoustic field.

According to further aspects of the invention which are advantageous but not compulsory, the method might incorporate one or several of the following features, taken in any technically admissible configuration:

• • At step d), the viscoelastic model (M) is built on the basis of the following equation:

$u_{i,\mathrm{ss}}\left(\overrightarrow{r}\right)=\frac{2\alpha I_0}{c}\sum _{j=1}^3\left(\left[S_j{\otimes }_{\overrightarrow{r}}{q}_{\mathrm{ij},\mathrm{ss}}\right]\left(\overrightarrow{r}\right)\right)$

• • where position and orientation in space are based on coordinate system (x₁,x₂,x₃), subscript i∈{1,2,3} represents a vector component in direction x_i, u_i({right arrow over (r)},t)=u(r,t)·{right arrow over (i)}, the same applying for any function, {right arrow over (r)} is a given position in the target region, defined by three coordinates (x₁,x₂,x₃), u_i,ss({right arrow over (r)}) is the component in the x_i direction of the steady-state displacement induced by the acoustic field at the given position {right arrow over (r)}, α is the ultrasound attenuation coefficient determined at step a), c is the speed of sound (c) determined at step c, I₀ is the amplitude of the intensity of the acoustic field at an arbitrary position {right arrow over (r₀)}, S_j({right arrow over (r)}) is the component in the x_j direction of the normalized intensity field at the given position {right arrow over (r)}, g_ij,ss({right arrow over (r)}) is the component along direction i of the steady-state Green's function of the soft solid, if the force excitation is in the j direction, at the given position {right arrow over (r)}, symbol [S_j⊗_{{right arrow over (r)}}g_ij,ss]({right arrow over (r)}) denotes convolution in space, at given position {right arrow over (r)}, of functions S_j and g_ij,ss.
  • At step d), the viscoelastic model (M′) is built on the basis of the following equation:

$\Delta u_{i,ss}\left(\stackrel{⟶}{r_1},\stackrel{⟶}{r_2}\right)=\frac{2\alpha I_0}{c}\sum _{j=1}^3\left(\left[S_j\otimes q_{ij,ss}\right]\left(\stackrel{⟶}{r_1}\right)-\left[S_j\otimes q_{\mathrm{ij},\mathrm{ss}}\right]\left(\stackrel{⟶}{r_2}\right)\right)$

• • where position and orientation in space are based on coordinate system (x₁,x₂,x₃), subscript i∈{1,2,3} represents a vector component in direction x_i, u_i({right arrow over (r)},t)={right arrow over (u)}({right arrow over (r)},t)·{right arrow over (i)}, the same applying for any function, {right arrow over (r₁)} is a first given position in the target region, {right arrow over (r₂)} is a second given position in the target region, Δu_i,ss({right arrow over (r₁)},{right arrow over (r₂)})=u_i,ss({right arrow over (r₁)})−u_i,ss({right arrow over (r₂)}) is the steady-state displacement difference induced by the acoustic field between the first and second given position, α is the ultrasound attenuation coefficient determined at step a), c is the speed of sound determined at step c), I₀ is the amplitude of the intensity of the acoustic field at an arbitrary position {right arrow over (r₀)}, S_j({right arrow over (r)}) is the time invariant shape of the acoustic field at the given position {right arrow over (r)}, g_ij,ss({right arrow over (r)}) is the steady-state Green's function of the soft solid at the given position {right arrow over (r)}, symbol [S_j⊗_{{right arrow over (r)}}g_ij,ss]({right arrow over (r)}) denotes convolution in space, at given position {right arrow over (r)}, of functions S_j and g_ij,ss.
  • The first and second given positions are located substantially at the same depth in the target region with respect to a source of the acoustic field.
  • The given position or one of the given positions at which the steady-state displacement is measured is a position where a position of the target region where a peak of intensity is expected.
  • During step f), the following elementary steps are implemented: f1) a first image of the target region is obtained by ultrasound scanning prior to step e); f2) a second image of the target region is obtained by ultrasound scanning at the end of or after step e) and f3) the measured steady-state displacement is determined by comparing the first and second images respectively obtained at steps f1) and f2).
  • The method includes a further step h) consisting in correcting (118) the measured value obtained at step f) by removing, from the value measured at step f), a displacement due to heating.
  • During step h), the following elementary steps are implemented: h1) a first image of the target region is obtained by ultrasound scanning prior to step e); h2) one waits for the target region to return to its initial position which existed prior to step e); h3) a third image of the target region is obtained by ultrasound scanning at the end of elementary step h1); h4) a thermal displacement artifact at the given position is determined by comparing the first and third images respectively obtained at steps h1) and h3) and h5) the steady-state displacement measured at step f) at a given position is corrected by subtraction of the value of the thermal displacement artifact at the given position.
  • The method includes a further step i) consisting in correcting any phase aberration of the acoustic field.
  • During step i), the following elementary steps are implemented: i1) a measured displacement image is generated for different delay laws; i2) the steady-state displacement image that should be produced by the acoustic field is calculated using the viscoelastic model; i3) a phase aberration is detected, based on a mismatch between the measured displacement image and the steady-state displacement image calculated using the viscoelastic model and i4) if it is detected, phase aberration is corrected iteratively, until the mismatch is minimized.
  • During step e), the ultrasound source is driven by a long burst, preferably in the form of a rectangle function, or by a succession of short bursts, each with a duration between 50 and 200 μs, and wherein the duration of the long burst or the duration of the succession of short bursts is preferably between 1 and 100 ms.
  • During step f), the displacement is measured by ultrasound imaging, by magnetic resonance imaging or by at least one optical method.
  • The values of the ultrasound attenuation coefficient and of the shear modulus are respectively measured at steps a) and b).

The invention also concerns an apparatus for implementing a method as mentioned here-above, characterized in that said apparatus comprises:

• • an acoustic source, for generating at step e) an acoustic field in the soft solid, for a duration such that it induces a steady-state localized deformation of the soft solid in the target region,
  • a measurement unit, including at least one sensor, for measuring at step f) a displacement induced by the acoustic field in the target region, as the steady-state deformation is present,
  • at least one determination unit for determining, at steps a), b) and c), the values of the ultrasound attenuation coefficient, of the shear modulus and of the speed of sound of the soft solid in the target region,
  • an electronic computation unit for building, with the values determined by the determination unit, the viscoelastic model of the steady-state displacement induced by the acoustic field generated by the acoustic source, and
  • an electronic computation unit for computing the amplitude of the intensity of the acoustic field at step g).

Such an apparatus is efficiently tailored to provide the same advantages as the method of the invention.

Advantageously, the electronic computation unit for building the viscoelastic model and the electronic computation unit for computing the amplitude of the intensity of the acoustic field are formed by a single piece of equipment.

Finally, the invention also concerns a therapeutic ultrasound process including steering of an ultrasound field towards a target region of a biological tissue, wherein the local intensity of the acoustic field is determined with a method as mentioned here-above.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be better understood on the basis of the following description which is given in correspondence with the appended figures and as an illustrative example, without restricting the object of the invention. In the annexed figures:

FIG. 1 is a block diagram of a first method according to the invention;

FIG. 2 is a is a schematic partial representation of an apparatus according to the invention, in use to implement the method of FIG. 1;

FIG. 3 is a schematic representation of a viscoelastic model used with the method of FIG. 1;

FIG. 4 is a block diagram of a second method according to the invention;

FIG. 5 is another a schematic partial representation of the apparatus of FIG. 1, in use to implement the method of FIG. 4; and

FIG. 6 is a schematic representation of a viscoelastic model used with the method of FIG. 4.

DETAILED DESCRIPTION OF SOME EMBODIMENTS

The apparatus A represented of FIG. 2 is designed to implement the method represented on FIG. 1. This apparatus A includes and ultrasonic array 2, which can be of any known type, for instance a linear array, a curved array, a phased array, a 2D matrix array, or a single element transducer. This ultrasonic array 2 is coupled to a box 4 and piloted by an electronic control unit or ECU 6 in order to direct an acoustic beam B, including a shear wave, towards the inside volume V4 of box 4. Thus ultrasonic array is a source for an acoustic field AF included in beam B and propagating in the direction of arrow A_B on FIG. 2.

S6 represents a signal sent by ECU 6 to array 2 in order to control this acoustic source.

A soft solid 8, for instance a biological tissue, is installed within volume V4 and a target region 82 of this soft solid is subjected to the acoustic beam B originating from acoustic source 2.

Alternatively, if soft solid can stand alone, box 4 can be omitted.

In this example, soft solid is a part of a muscle of an animal to be studied.

According to a known feature of acoustic emitters/receptors, acoustic array 2 is also configured as a scanner for detecting an image of soft solid 8, this image showing the location of several positions of this soft solid within target region 82.

S2 represents a signal sent by ultrasonic array 2 to ECU 6, this signal S2 being representative of the scanned image detected.

Alternatively, two different pieces of equipment can be used instead of array 2, that is one for emitting beam B and another one for scanning the image of target region 82.

ECU 6 includes some electronic components, such as one or several microprocessors and one or several memories, and some computer programs to automatically implement the method of the invention.

When beam B is applied to soft solid 8, it is essential to know the effect of this beam within this soft solid. This effect depends on the local intensity of the acoustic field AF. This local intensity can be determined with the method of the invention.

Let u denote a displacement observed at a given position within target region 82 and {right arrow over (i)} denote the instantaneous acoustic field intensity vector, or Poynting vector, at the same position.

First Method of the Invention

The method of the invention relies upon the fact that the acoustic field intensity {right arrow over (i)}, at a given position within target region 82, can be considered as proportional to a force F applied to this position. On the other hand, the displacement u of the soft solid at this position can also be considered as proportional to a weighted sum of forces. Thus, a proportionality relationship exists between the acoustic field intensity {right arrow over (i)} and the displacement u obtained at the same position.

A viscoelastic model M, such as the one represented on FIG. 3, can thus be considered as establishing a relationship between the intensity and the displacement.

Note here that the viscoelastic model M is not necessarily linear. In other words, the curve of FIG. 3 does not need to be a straight line.

The method of the invention also relies on the fact that, if the displacement u and the viscoelastic model M are known, an inversion of the viscoelastic model M allows determination of the acoustic field intensity {right arrow over (i)}.

On the other hand, according to the literature, in particular Bercoff et al. cited here-above, the viscoelastic model M depends, amongst others, on the following three parameters:

• • the ultrasound attenuation coefficient α of the soft solid 8 in the target region 82;
  • the shear modulus μ of the soft solid 8 in the target region 82; and
  • the speed of sound c in the target region of the soft solid.

A first method according to the invention is schematically represented on FIG. 1.

Determination of Parameters α, μ and c

In a first step 100, the method begins and some memories of ECU 6 are emptied or reset.

In a subsequent step 102, the ultrasound attenuation coefficient α is determined, either by access to the literature or experimentally, as taught by Ophir et al in Ophir J, in. “Attenuation estimation in reflection: progress and prospects”. (Ultrason Imaging. 1984 October; 6(4):349-95. Review), whose content is incorporated herein by reference.

In another step 104, the shear modulus μ is determined, either by access to the literature or experimentally, as taught by Muthupillai et al in “Magnetic resonance elastography by direct visualization of propagating acoustic strain waves” (Science. 1995 Sep. 29; 269(5232):1854-7) or by Sarvazyan et al in “Shear wave elasticity imaging: a new ultrasonic technology of medical diagnostics” (Ultrasound Med Biol. 1998 November; 24(9):1419-35) whose content is incorporated herein by reference.

At step 104, experimental estimation of the shear modulus μ involves

• • i)—inducing a shear wave in the region of interest, that is in the target region 82 where this shear modulus is being determined and
  • ii)—estimating a displacement in that region, and
  • iii)—processing the displacement image to determine the shear modulus.

Estimation of the shear modulus is not possible in the region where the shear wave is induced. Hence, in step i mentioned here above, the shear wave is initiated in the vicinity of the target region of interest, but not exactly at the region of interest.

In another step 106, the speed of sound c is derived from the literature. Alternatively, it can be measured.

Steps 102, 104 and 106 can be simultaneous or occur in any order. Each of these steps includes an operation of storing, in a memory of ECU 6, the value of the parameter detected.

Building of a Viscoelastic Model

In order to be able to actually compute a viscoelastic model and invert it at a later stage one uses assumptions allowing simplification.

The first assumption is that the acoustic field AF whose intensity {right arrow over (i)} is to be determined is steady invariant in time. In other words, this acoustic field is supposed to have a constant intensity, even if this field induces vibration over time of some particles in the target region 82.

The second assumption is that the acoustic field is applied for a duration such that the acoustic field induces a steady-state localized deformation of the soft solid in the target region.

Let {right arrow over (i)}({right arrow over (r)}, t) represent the instantaneous acoustic intensity vector, or Poynting vector, at a given position {right arrow over (r)} and time t. Assume that the acoustic wave is cyclic, with repetition time T. Let {right arrow over (I)}({right arrow over (r)}, t) represent the time averaged acoustic intensity vector. Let I({right arrow over (r)}, t) be the amplitude of the time-averaged intensity vector.

By definition, the following equation prevails:

$\begin{array}{cc}\overrightarrow{I}\left(\overrightarrow{r},t\right)=\frac{1}{T}{\int }_{t-\frac{T}{2}}^{t+\frac{T}{2}}\overrightarrow{i}\left(\overrightarrow{r},t^{\prime }\right){\mathrm{dt}}^{\prime }I\left(\overrightarrow{r},t\right)=\overrightarrow{I}\left(\overrightarrow{r},t\right)& \left(1\right)\end{array}$

The radiation force distribution {right arrow over (f)}({right arrow over (r)}, t) induced by the acoustic field is given by Torr et al in “The acoustic radiation force” (American Journal of Physics 1984; 52(5):402-8) whose content is incorporated by reference. The following equation prevails:

$\begin{array}{cc}\stackrel{\to }{f}\left(\overrightarrow{r},t\right)=\frac{2\alpha }{c}\overrightarrow{I}\left(\overrightarrow{r},t\right)& \left(2\right)\end{array}$ where α is the attenuation coefficient of sound and c is the speed of sound identified here above.

The displacement distribution {right arrow over (u)}({right arrow over (r)}, t) induced by the radiation force in a homogeneous isotropic viscoelastic medium is given by Bercoff et al in “The role of viscosity in the impulse diffraction field of elastic waves induced by the acoustic radiation force” (IEEE Trans Ultrason Ferroelectr Freq Control. 2004 November; 51(11):1523-36), whose content is incorporated by reference. The following equation prevails:u_i({right arrow over (r)},t)=Σ_j=1³([f_j{circle around (×)}_{{right arrow over (r)},t}g_ij]({right arrow over (r)},t))  (3)where

• • Position and orientation in space are based on the coordinate system (x₁,x₂,x₃),
  • Subscripts i and j represent components of a vector, along directions x_i and x_j respectively
    • u_i({right arrow over (r)},t)={right arrow over (u)}({right arrow over (r)},t)·{right arrow over (x)}_i, with i∈{1,2,3}
    • f_j({right arrow over (r)},t)={right arrow over (f)}({right arrow over (r)},t)·{right arrow over (x)}_j, with j∈{1,2,3}
  • {right arrow over (g)}({right arrow over (r)},t) is the viscoelastic Green's function of the soft solid 8,
  • g_ij is the component along direction i of the Green's function {right arrow over (g)}({right arrow over (r)},t) when the force excitation is exerted in direction j,
  • and symbol [f{circle around (×)}_{{right arrow over (r)},t}g]({right arrow over (r)},t) denotes convolution in space and time of functions f and g. This convolution is defined by the following relationship:

$\left[f{\otimes }_{\overrightarrow{r},t}g\right]\left(\overrightarrow{r},t\right)\underset{\mathrm{def}}{=}\int \int \int {\int }_{-\infty }^{+\infty }f\left(x_1^{\prime },x_2^{\prime },x_3^{\prime },t^{\prime }\right)·g\left(x_1-x_1^{\prime },x_2-x_2^{\prime },x_3-x_3^{\prime },t-t^{\prime }\right)·{\mathrm{dx}}_1^{\prime }·{\mathrm{dx}}_2^{\prime }·{\mathrm{dx}}_3^{\prime }·{\mathrm{dt}}^{\prime }$

The Green's function also depends on parameters μ, η, α and c, where η is the shear viscosity in the soft solid 8. Hence the symbol {right arrow over (g)}({right arrow over (r)},t) is actually a shorthand notation for {right arrow over (g)}({right arrow over (r)},t,α,c,μ,η).

In the most general case, the displacement distribution induced by the instantaneous acoustic intensity can be predicted in some region of interest, by combining equations (2) and (3).

In most applications, the acoustic beam B exhibits a specific pattern, or shape, in space. Moreover, its intensity is modulated to follow a specific waveform in time. Shaping in space is typically achieved electronically using focusing or “beamforming” techniques for driving ultrasonic source 2. Modulation in time is typically achieved by driving the setup with specific acoustic power waveforms. For example, the acoustic power waveform may be a rectangle function, resulting in constant power being applied over a specific duration. Assuming that the shape of the acoustic field is time-invariant, as mentioned in the first assumption here above, the intensity distribution can be as mentioned in the following equation:{right arrow over (I)}({right arrow over (r)},t)=I₀·W(t)·{right arrow over (S)}({right arrow over (r)})  (4)where I₀ is the peak value of local intensity, {right arrow over (r₀)} is the position where this peak is expected to occur, the vector field {right arrow over (S)}({right arrow over (r)}) represents the shape of the beam, i.e. the spatial distribution of acoustic intensity with amplitude normalized by I₀, and scalar function W(t) represents the temporal waveform of acoustic intensity, also normalized by I₀. I₀. can also be considered as the amplitude of the intensity of the acoustic field at an arbitrary position {right arrow over (r₀)}

Under these assumptions, equation (3) becomes:

$\begin{array}{cc}{u}_i\left(\overrightarrow{r},t\right)=\frac{2\alpha I_0}{c}\sum _{j=1}^3\left(\left[W{\otimes }_t{S}_j{\otimes }_{\overrightarrow{r}}{g}_{\mathrm{ij}}\right]\left(\overrightarrow{r},t\right)\right)& \left(5\right)\end{array}$ where S_j({right arrow over (r)}) is the component in the x_j direction of the normalized intensity field at the given position {right arrow over (r)}, in other words the shape of the acoustic field.

Equation (5) shows that the entire displacement distribution u_i({right arrow over (r)},t) is proportional to peak intensity I₀. As a consequence, the experimental value of peak intensity I₀ can be estimated in three steps, namely:

• • Using equation (5) to calculate a simulated displacement u_i,sim induced by some arbitrary intensity value I₀=I_0,sim at some arbitrary position {right arrow over (r₁)},
  • Performing an experiment and measuring the displacement u_i,exp at the same position {right arrow over (r₁)},
  • Estimating intensity I_0,exp using the following equation:

$\begin{array}{cc}{I}_{0,\exp }=I_{0,\mathrm{sim}}\frac{u_{i,\exp }\left(\stackrel{⟶}{r_1}\right)}{u_{i,\mathrm{sim}}\left(\stackrel{⟶}{r_1}\right)}& \left(6\right)\end{array}$

The position {right arrow over (r₁)} is preferably chosen to be at the location {right arrow over (r₀)} of the intensity peak I₀, or in its vicinity, so that u_i,exp({right arrow over (r₁)}) is maximum and can be determined with high precision.

The computations leading to equation (6) constitute an inversion of the viscoelastic model M represented of FIG. 3.

Since the spatial distribution of the intensity {right arrow over (i)} is as shown in equation (4) and since functions W(t) and {right arrow over (S)}({right arrow over (r)}) are known, it is enough to know I_o,exp in order to know {right arrow over (I)}({right arrow over (r)},t).

A first limitation of the technique described above is that shear viscosity i is usually unknown in biological tissues. A solution can be found using steady-state displacement, as mentioned here-above with the second assumption. During steady-state, viscous forces are nulled, and the resulting displacement is independent of shear viscosity.

Steady-state condition is achieved using long excitation with constant power for exiting the ultrasound array 2. In this example, the corresponding excitation waveform W(t) may be a Heaviside function:

$\begin{array}{cc}W\left(t\right)=|\begin{array}{cc}0& t<0\\ 1/2& t=0\\ 1& t>0\end{array}& \left(7\right)\end{array}$

The component in the x_i direction of the steady-state displacement is given by:

$\begin{array}{cc}{u}_{i,\mathrm{ss}}\left(\overrightarrow{r}\right)=\frac{2\alpha I_0}{c}\sum _{j=1}^3\left(\left[S_j{\otimes }_{\overrightarrow{r}}{g}_{\mathrm{ij},\mathrm{ss}}\right]\left(\overrightarrow{r}\right)\right)& \left(8\right)\end{array}$ where

$g_{\mathrm{ij},\mathrm{ss}}\left(\overrightarrow{r}\right)=\underset{t\to +\infty }{\lim }\left({\int }_0^t{g}_{\mathrm{ij}}\left(\overrightarrow{r},t^{\prime }\right){\mathrm{dt}}^{\prime }\right)$ is the steady-state Green's function of the medium, i.e. the displacement field induced by a Heaviside excitation force applied at a position source. Equation (8) is obtained by plugging equation (7) into equation (5), then writing the convolution product in integral form, and replacing W(t) by 1 for t>0.

Thus, the displacement u induced at one or several position(s) of interest {right arrow over (r)} by the acoustic field may be pre-calculated for any intensity value I₀, using equation (8) and the values α, and μ and c determined in steps 102, 104 and 106. This allows creating, in a further step 108, a displacement image DI of the soft solid in target region 82, by grouping the displacement values of the different positions of interest.

It is possible to work with one position of interest {right arrow over (r)} only. In such a case, the displacement image DI includes one pixel only, which corresponds to the displacement u pre-calculated for this position of interest.

The displacement images DI, that is the displacement values, obtained at steps 108 are then used in a subsequent step 110, in order to build a viscoelastic model M, which is a relationship between the local intensity I₀ of the acoustic beam B and the induced displacement u. For each direction (i=1, 2 or 3) of the coordinate system, this model can take the shape represented by the curve of FIG. 3. In other words, the curve of FIG. 3, a straight line in this example, forms an abacus or a calibration chart of the viscoelastic model M.

In the most general case, and especially when high acoustic intensity is being used, nonlinear wave propagation may occur. The relationship between displacement and intensity can take any shape, such as the one illustrated in FIG. 6 for the second embodiment of the invention.

In order to build the calibration chart, step 108 is repeated for different intensities I₀ of acoustic beam B.

However in the specific case of low acoustic intensity, acoustic wave propagation can be assumed to be linear. The relationship between displacement and intensity is a straight line, as illustrated in FIG. 3. In this specific case, step 108 needs to be performed only once, with some arbitrary intensity I₀, to determine the slope of the line.

Alternatively, the model can be an elastic model, as taught by Calle et al. in “Temporal analysis of tissue displacement induced by a transient ultrasound radiation force” (J Acoust Soc Am. 2005 November; 118(5):2829-40).

Steps 100 to 110 represent preparatory steps for the subsequent steps of the method of the invention, where the viscoelastic model will be used, as explained here-after.

Determination of Local Field Intensity

When the local intensity of the acoustic field AF is to be determined, one implements a further step 112 of the method where the acoustic field AF is applied to the target region 82.

Thereafter, the displacement u induced by the acoustic field is determined in a further step 114.

In step 114, a second displacement image DI′ of the soft solid in target region 82 is created. This second displacement image DI′, which is an image of the displacement u induced by the acoustic field, is determined by an ultrasound technique, as taught by Ophir et al in “Elastography: a quantitative method for imaging the elasticity of biological tissues” (Ultrason Imaging. 1991 April; 13(2):111-34) whose content is incorporated herein by reference.

With this ultrasound technique, estimation of the displacement induced by the ultrasonic beam to be measured involves the following elementary steps

• • iv)—using the ultrasound scanner 2 to acquire and store, in a memory of ECU 6, a first image I₁ of the region of interest prior to applying the acoustic field,
  • v)—generating the acoustic beam B whose intensity is to be measured,
  • vi)—using the ultrasound scanner 2 to acquire and store, in a memory of ECU 6, a second image I₂ of the region of interest and
  • vii)—estimating local displacement in each pixel by comparing the ultrasound images I₁ and I₂ acquired in steps iv and vi.

Each position of volume V4 is observed in a coordinate system (x₁,x₂,x₃).

Each pixel of an image I₁ or I₂ represents the local displacement undergone by this pixel along a chosen direction; for example along direction x₃ in the coordinate system (x₁,x₂,x₃), the direction being parallel to arrow A_B.

Equation (8) shows that the entire displacement distribution u_i,ss({right arrow over (r)}) is proportional to peak intensity I₀. As a consequence, the experimental value of peak intensity can be estimated in three steps:

• • Using equation (8) to calculate the steady-state displacement u_i,ss,sim induced by some arbitrary intensity value I₀=I_0,sim at some arbitrary position {right arrow over (r₁)},
  • Performing an experiment and measuring the steady-state displacement u_i,ss,exp at the same position {right arrow over (r₁)},
  • Estimating intensity I_0,exp using:

$\begin{array}{cc}{I}_{0,\exp }=I_{0,\mathrm{sim}}\frac{u_{i,\mathrm{ss},\exp }\left(\stackrel{⟶}{r_1}\right)}{u_{i,\mathrm{ss},\mathrm{sim}}\left(\stackrel{⟶}{r_1}\right)}& \left(9\right)\end{array}$ In practice, steady-state localized deformation at step 112 can be approximated by driving the acoustic array or source 2 with a burst having constant power and long duration T:

$\begin{array}{cc}W\left(t\right)=\mathrm{rect}\left(t/T\right)|\begin{array}{cc}0& ❘t❘>T/2\\ 1/2& ❘t❘=T/2\\ 1& ❘t❘<T/2\end{array}& \left(10\right)\end{array}$

In other words, the rectangle function used to drive the acoustic source 2 at step 112 equals 1 between t=−T/2 and t=+T/2 and 0 otherwise. The rectangle function is a long burst between t=−T/2 and t=+T/2. In practice, the value of T is chosen between 0.1 and 1000 milliseconds (ms), preferably between 1 and 100 ms.

Alternatively, other functions can be used to define the shape and/or duration of application of the ultrasound beam. In particular, excitation can be made by a succession of short bursts, with a duration between 50 and 200 microseconds (μs) each, where the total duration of the bursts train is between 0.1 and 1000 ms, preferably between 1 and 100 ms.

The steady-state displacement is approximated by a measurement performed at step 114, immediately after the end of the excitation burst:u_i,ss({right arrow over (r₁)})≈u_i({right arrow over (r₁)},T/2)  (11)

By “immediately”, one means that measure of displacement takes place within 0 and 10 ms, preferably within 0 and 0.1 ms after the end of the application of the acoustic field.

Alternatively, the second displacement image DI′ is created at step 114 by MRI technique (Magnetic Resonance Imaging), as taught by Muthupillai et al in “Magnetic resonance elastography by direct visualization of propagating acoustic strain waves” (Science. 1995 Sep. 29; 269(5232):1854-7), as taught by McDannold and Meier “Magnetic resonance acoustic radiation force imaging” (Med Phys. 2008; 35(8):3748-58) or as taught by Souchon et al in “Transient MR elastography (t-MRE) using ultrasound radiation force: theory, safety, and initial experiments in vitro” (Magn Reson Med. 2008 October; 60(4):871-81), whose content is incorporated by reference.

According to another alternative approach, at step 114, the displacement can be measured by one or several optical methods.

Then, in a subsequent step 116, the intensity is computed on the basis of model M. Consider that a value u_m has been measured at a given position for displacement u at step 114. It is then possible to access model M in order to determine which value i_m of the intensity corresponds to value u_m, as shown by the dotted lines in FIG. 3. In other words, model M is inverted in step 116 in order to compute the intensity of the acoustic field AF.

The goal of the invention is reached and one can, on the basis of the value computed in step 116, react to an attenuation or deflection of the beam B within target region 82.

Second Method of the Invention

The first method described here above, which is according to a first embodiment of the invention, gives good results.

However, it makes the assumption that the medium of the soft solid 8 is homogeneous. Such an assumption is not always valid, in particular for biological tissues.

In such a case, a possible solution consists in developing a model for heterogeneous media, for example using finite elements as taught by Palmeri et al in “A finite-element method model of soft tissue response to impulsive acoustic radiation force” (IEEE Trans Ultrason Ferroelectr Freq Control. 2005 October; 52(10):1699-712). However this approach requires exact knowledge of the viscoelastic properties of the tissues along the entire propagation path of the beam. In medical applications, these properties are usually unknown, or they are known with substantial uncertainty.

The second method of the invention represented on FIGS. 4 to 6 allows handling such a case. This alternative method of the invention is based on an approach consisting in removing the contribution of heterogeneous regions.

In the description here below, steps of the methods and parts of the associated apparatus which are the same as in the first embodiment have the same references. Hereafter, only the differences with respect to the first embodiment are detailed.

Assume the force distribution {right arrow over (f)}({right arrow over (r)}) in any position {right arrow over (r)} of the target region can be separated in two parts, that is:

• • local forces {right arrow over (f_local)}({right arrow over (r)}) acting in the vicinity of observation position {right arrow over (r)}, and
  • remote forces {right arrow over (f_remote)}({right arrow over (r)}) acting at a distance from that position.

The following equation prevails:{right arrow over (f)}({right arrow over (r)})={right arrow over (f_local)}({right arrow over (r)})+{right arrow over (f_remote)}({right arrow over (r)})  (12)

A local region 82A corresponds to a small region of interest, where acoustic intensity is to be determined. This local region is a sub-part of target region 82. The local region 82A is assumed to be locally homogeneous. The remote region, that is the remaining part of soft solid 8 outside of local region 82A, can be heterogeneous. The steady-state displacement {right arrow over (u_SS)}({right arrow over (r)}) can be decomposed as the sum of the displacement {right arrow over (u_SS,local)}({right arrow over (r)}) induced by forces acting locally, that is in local region 82A, and of displacement {right arrow over (u_SS,remote)}({right arrow over (r)}) induced by remote forces acting at a distance. The following equation prevails:{right arrow over (u_SS)}({right arrow over (r)})={right arrow over (u_SS,local)}({right arrow over (r)})+{right arrow over (u_SS,remote)}({right arrow over (r)})  (13)

Consider two observation positions {right arrow over (r₁)} and {right arrow over (r₂)} located within the local region of interest 82A, and close to each other. The steady-state displacement {right arrow over (u_SS,remote)}({right arrow over (r₂)}) induced by remote static forces at position {right arrow over (r₂)} will be almost identical to the steady-state displacement {right arrow over (u_SS,remote)}({right arrow over (r₁)}) induced at position {right arrow over (r₁)}. In other words, the following equation prevails:

$\begin{array}{cc}\stackrel{⟶}{u_{\mathrm{SS},\mathrm{remote}}}\left(\overrightarrow{r_2}\right)=\stackrel{⟶}{u_{\mathrm{SS},\mathrm{remote}}}\left(\overrightarrow{r_1}\right)+\underset{\underset{\mathrm{negligible}}{︸}}{\delta \stackrel{⟶}{u_{\mathrm{SS},\mathrm{remote}}}}& \left(14\right)\end{array}$

Now, consider the difference {right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)}) defined by:{right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)})={right arrow over (u_SS)}({right arrow over (r₁)})−{right arrow over (u_SS)}({right arrow over (r₂)})  (15)

Using the decomposition in local and remote contributions, as defined in equation 13, and noting that remote contributions are nearly identical, as shown in equation 14, equation (15) becomes:{right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)})≈{right arrow over (u_SS,local)}({right arrow over (r₁)})−{right arrow over (u_SS,local)}({right arrow over (r₂)})  (16)

In conclusion, the difference in displacement {right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)}) undergone at two neighboring positions depends mostly on local forces. It is almost independent of the forces acting on the remote region.

The difference {right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)}) can therefore be calculated in a simulation wherein forces acting at a distance, in the heterogeneous remote region, are ignored. Only local forces acting within the homogeneous region of interest 82A need be accounted for. In this region, the homogeneous Green's function model of equation 8 can be used, and the difference in displacement {right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)}) can be expressed in the following equation:

$\begin{array}{cc}\Delta u_{i,\mathrm{ss}}\left(\overrightarrow{r_1},\overrightarrow{r_2}\right)=\frac{2\alpha I_0}{c}{\sum }_{j=1}^3\left(\left[S_j\otimes g_{\mathrm{ij},\mathrm{ss}}\right]\left(\overrightarrow{r_1}\right)-\left[S_j\otimes g_{\mathrm{ij},\mathrm{ss}}\right]\left(\overrightarrow{r_2}\right)\right)& \left(17\right)\end{array}$

Equation (17) shows that the difference {right arrow over (Δu_SS)}({right arrow over (r₁)},{right arrow over (r₂)}) is proportional to peak intensity I₀.

The method of FIG. 4 differs from the method of FIG. 1 in that the model M′ calculated in step 110 is a model of the difference {right arrow over (Δu_SS)} in displacement, not a model of displacement, as in the first embodiment. Moreover, the model M′ is not linear.

In this second method of the invention, the experimental value of peak intensity can be estimated in four main steps:

• • in step 110, using equation (17) to calculate the difference Δu_i,ss,sim({right arrow over (r₁)},{right arrow over (r₂)}) induced at some arbitrary positions {right arrow over (r₁)} and {right arrow over (r₂)} by an acoustic field AF having peak intensity value I₀=I_0,sim, where I_0,sim can be chosen arbitrarily;
  • in step 112, performing an experiment where the acoustic field AF is applied to the target region 82 as explained for the first embodiment;
  • in step 114, measuring two displacements {right arrow over (u_SS)}({right arrow over (r₁)}), {right arrow over (u_SS)}({right arrow over (r₂)}) and using equation (15) to determine the experimental value of the difference Δu_i,ss,exp({right arrow over (r₁)},{right arrow over (r₂)}) at the same positions {right arrow over (r₁)} and {right arrow over (r₂)}; and
  • in step 116, estimating intensity I_0,exp by inversion of the model M′, or in other words, by determining intensity I_0,exp from the calibration chart of FIG. 6, given that displacement difference Δu_i,ss,exp({right arrow over (r₁)},{right arrow over (r₂)}) is now known.

Alternatively, in step 116, in the specific case of a linear model, as the one illustrated in FIG. 3, the calibration chart is a straight line, and intensity is determined by using the following equation:

$\begin{array}{cc}{I}_{0,\exp }=I_{0,\mathrm{sim}}\frac{\Delta u_{i,\mathrm{ss},\exp }\left(\overrightarrow{r_1},\overrightarrow{r_2}\right)}{\Delta u_{i,\mathrm{ss},\mathrm{sim}}\left(\overrightarrow{r_1},\overrightarrow{r_2}\right)}& \left(18\right)\end{array}$

In practice, according to an advantageous aspect of the invention, in order to minimize the value of δ{right arrow over (u_SS,remote)}, the positions {right arrow over (r₁)} and {right arrow over (r₂)} for which the displacement difference is considered are chosen at the same depth or approximatively at the same depth, with respect to the ultrasound source 2, within the target region 82. Consider the center C₂ of ultrasound array 2, that is the center of the emission of beam B. One can choose that positions {right arrow over (r₁)} and {right arrow over (r₂)} are located at the same distance d of this center C₂, that is, in the plane of FIG. 5, on a circle C₈₂ centered on center C₂ and having a radius equal to distance d.

Preferably, one of the two positions {right arrow over (r₁)} and {right arrow over (r₂)} is chosen equal to the location {right arrow over (r₀)} where the peak I₀ of the intensity is expected to occur.

Optional Temperature Correction

For the two methods mentioned here above, local heating induced by the acoustic beam may result in artifacts in the displacement image obtained at steps 108 and 114. For small changes in temperature, typically within +/−10° C., this phenomenon is mostly due to speed of sound changing with temperature, as taught by Seip et al in “Noninvasive estimation of tissue temperature response to heating fields using diagnostic ultrasound” (IEEE Trans Biomed Eng. 1995 August; 42(8):828-39) or by Souchon et al in “Monitoring the formation of thermal lesions with heat-induced echo-strain imaging: a feasibility study” (Ultrasound Med Biol. 2005 February; 31(2):251-9), whose content is incorporated by reference.

Artifacts due to heating are corrected by an additional step 120 taking place between steps 114 and 116 of the second method, where the displacement due to heating is removed from the steady-state displacement value measured at step 114. More precisely, this step 120 includes the following elementary steps:

• • viii)—waiting for the soft solid to return to its initial position
  • ix)—creating a displacement image, as described in steps vi and vii, said displacement image being considered to be representative of the displacement artifact induced by heat,
  • x)—correcting the displacement image by subtracting, in each pixel, the artifactual displacement from the measurement previously obtained in step 114.

In other words, a first image I₁ of the target region is obtained by ultrasound scanning prior to step 112. Then, one implements steps 112 and 114. Then one waits for the target region to return to its initial position which existed prior to step 112, as mentioned in elementary step viii). Thereafter, a third image of the target region is obtained by ultrasound scanning at the end of elementary step viii). A thermal displacement at the given position ({right arrow over (r)}) can then be determined by comparing the first and third images I₁ and I₃ respectively obtained. This corresponds to elementary step ix). Then, at step x), the steady-state displacement (u_i,ss({right arrow over (r)})) measured at step 114 at a given position ({right arrow over (r)}) is corrected by subtraction of the value of the thermal displacement at the given position.

Alternatively, the corrected displacement is obtained directly by comparing the second image of the medium or soft solid 8, which was acquired during step 114, and the third image of the medium.

The time delay between step 114 and elementary step ix), that is the duration of step viii), must be long enough so that the medium or soft solid 8 has time to return to its initial position, and short enough so that cooling is negligible. A typical value for this time delay is between 1 and 100 ms.

Optional Phase Aberration Correction

The geometric distortion possibly undergone by the acoustic beam B, while propagating in the soft solid 8, is called phase aberration. This might induce some perturbation of the measured displacement.

Phase aberration can be corrected by applying time delays to the elements of the acoustic source. A set of time delays is called a delay law. The time delays are adapted to the medium, in other words to the soft solid 8. Such correction requires that the source is composed of multiple elements.

Thus, in a further step 122, phase aberration is detected based on the difference between the experimental displacement image obtained at step 114 and the displacement image expected from simulations for the set value of the spatial distribution of the acoustic field intensity computed with the model M′ at step 110. In this step 122, phase aberration is corrected iteratively, until the mismatch is minimized. Here, one can make use of the teachings of Herbert et al in “Energy-based adaptive focusing of waves: application to noninvasive aberration correction of ultrasonic wavefields” (IEEE Trans Ultrason Ferroelectr Freq Control. 2009 November; 56(11):2388-99) whose content is incorporated by reference. Iteration is shown by arrow 124 on FIG. 4.

In other words, a measured displacement image can be generated for different given positions. Then, a possible phase aberration is detected, based on a mismatch between the measured displacement image and a displacement image expected from simulation. If is detected, phase aberration is corrected iteratively, until the mismatch is minimized.

On FIG. 4, step 122 is represented after step 120. However these steps can take place in any order.

General Remarks

The methods and apparatus described here above can be combined to generate new embodiments of the invention, within the scope of the attached claims. In particular, steps 120 and/or 122 can also be implemented with the method of FIG. 1.

The invention is described here above in case one uses a Green's function to build the viscoelastic model M. However, other approaches can be performed to do so, such as the finite differences method, or using the finite elements method described by Eskandari et al. in “Viscoelastic characterization of soft tissue from dynamic finite element models” (Physics in medicine and biology 2008; 53(22): 6569-90).

Similarly, inversion of the viscoelastic model M can be performed with techniques alternative to the ones leading to equation (6). In particular, one can use any of the methods described in the book “Parameter Estimation and Inverse Problems”, (2018), Third Edition, Elsevier. ISBN 9780128134238, ISBN 9780128134238″ by Aster Richard; Borchers Brian, and Thurber Clifford, whose content is included in this description by reference.

As explained here above, a therapeutic ultrasound process can be implemented, wherein an ultrasound field is steered towards a target region of a biological tissue and wherein the local intensity of the acoustic field is determined with a method as explained here-above.

However, the invention is not limited to diagnostic or therapeutic ultrasound applications. It can be used to characterize different types of animal or vegetal soft solids and natural or synthetic soft material in cosmetic or food industry, in particular for quality control purposes. The invention can also be used to characterize non-metallic portions of prostheses. The invention can also be used to treat such soft solids, in particular to improve some of their physical characteristics.

Claims

1. Method for determining a local intensity of an acoustic field induced by an ultrasound source and propagating in a target region of a soft solid, at a position located within said target region, wherein said method includes at least the following steps: a) determining a value of an ultrasound attenuation coefficient of the soft solid in the target region;b) determining a value of the shear modulus of the soft solid in the target region;c) determining a value of the speed of sound in the target region of the soft solid;d) building, with the values determined in steps a), b) and c), a viscoelastic model of a steady-state displacement induced by an acoustic field having a time invariant shape, or a viscoelastic model of a difference between two steady-state displacements induced by an acoustic field having a time invariant shape;e) applying, to the target region the acoustic field emitted by an ultrasound source, for a duration such that the acoustic field induces a steady-state localized deformation of the soft solid in the target region;f) measuring at least one steady-state displacement, or a steady-state displacement difference, induced by the acoustic field at a given position in the target region; andg) computing an amplitude of the intensity of the acoustic field at said given position by inverting the viscoelastic model built at step d) at said given position, for the displacement(s) measured at step f).

2. The method according to claim 1, wherein, at step d), the viscoelastic model of the steady-state displacement is built on the basis of the following equation:

3. The method according to claim 1, wherein, at step d), the viscoelastic model of the difference between two steady-state displacements is built on the basis of the following equation:

4. The method according to claim 3, wherein the first and second given positions are located substantially at the same depth in the target region with respect to a source of the acoustic field.

5. The method according to claim 1, wherein the given position or one of the given positions at which the steady state displacement is measured is a position where a position of the target region where a peak of intensity is expected.

6. The method according to claim 1, wherein, during step f), the following elementary steps are implemented: f1) a first image of the target region is obtained by ultrasound scanning prior to step e)f2) a second image of the target region is obtained by ultrasound scanning at the end of or after step e)f3) the measured steady-state displacement is determined by comparing the first and second images respectively obtained at steps f1) and f2).

7. The method according to claim 1, wherein it includes a further step h) consisting in correcting the measured value obtained at step f) by removing, from the value measured at step f), a displacement due to heating.

8. The method according to claim 7, wherein during step h), the following elementary steps are implemented: h1) a first image of the target region is obtained by ultrasound scanning prior to step e)h2) one waits for the target region to return to its initial position which existed prior to step e)h3) a third image of the target region is obtained by ultrasound scanning at the end of elementary step h1)h4) a thermal displacement artifact at the given position is determined by comparing the first and third images respectively obtained at steps h1) and h3)h5) the steady state displacement measured at step f) at a given position is corrected by subtraction of the value of the thermal displacement artifact at the given position.

9. The method according to claim 1, wherein it includes a further step i) consisting in correcting any phase aberration of the acoustic field.

10. The method according to claim 9, wherein during step i), the following elementary steps are implemented: i1) a measured displacement image is generated for different delay laws;i2) the steady-state displacement image that should be produced by the acoustic field is calculated using the viscoelastic model;i3) a phase aberration is detected, based on a mismatch between the measured displacement image and the steady-state displacement image calculated using the viscoelastic model; andi4) if it is detected, the phase aberration is corrected iteratively, until the mismatch is minimized.

11. The method according to claim 1, wherein during step e), the ultrasound source is driven by a long burst, preferably in the form of a rectangle function, or by a succession of short bursts, each with a duration between 50 and 200 μs, and wherein the duration of the long burst or the duration of the succession of short bursts is preferably between 1 and 100 ms.

12. The method according to claim 1, wherein, during step f), the displacement is measured by ultrasound imaging, by magnetic resonance imaging or by at least one optical method.

13. The method according to claim 1, wherein the values of the ultrasound attenuation coefficient and of the shear modulus are respectively measured at steps a) and b).

14. Apparatus for implementing a method according to claim 1, implemented by applying an acoustic field to a target region of a soft solid, wherein said apparatus comprises: an acoustic source for generating at step e) the acoustic field in the soft solid, for a duration such that it induces a steady-state localized deformation of the soft solid in the target region,a measurement unit, including at least one sensor for measuring at step f) a displacement induced by the acoustic field in the target region, as the steady-state deformation is present,at least one determination unit for determining, at steps a), b) and c), the values of the ultrasound attenuation coefficient, of the shear modulus and of the speed of sound of the soft solid in the target region,an electronic computation unit for building, with the values determined by the determination unit, the viscoelastic model of the steady-state displacement induced by the acoustic field generated by the acoustic source, andan electronic computation unit for computing an amplitude of the intensity (i) of the acoustic field at step g).

15. The apparatus according to claim 14, wherein the measurement unit, the electronic computation unit for building the viscoelastic model and the electronic computation unit for computing the amplitude of the intensity of the acoustic field are formed by a single piece of equipment.

16. A therapeutic ultrasound process including steering of an ultrasound field towards a target region of a biological tissue, wherein the local intensity of the acoustic filed is determined with a method according to claim 1.