Chapter 8

Anomaly Estimation and Layer Potential Techniques

Layer potential techniques have been used widely to deal with the inverse problem of recovering anomalies in a homogeneous background. The reason is that the method provides a concrete expression connecting the anomalies with measured data.

For example, consider the inverse problem of detecting an electrical conductivity anomaly, occupying a region D, inside a three-dimensional region Ω bounded by its surface ∂Ω. Assume that the complex conductivity distribution images at angular frequency ω changes abruptly across the boundary ∂D and images in images. With the aid of the fundamental solution F(r): = − 1/(4π|r|) of the Laplacian, we can provide a rigorous connection between the anomaly D and the boundary voltage–current data via the following integral equation (Kang and Seo 1996): for images,

8.1 8.1

where g represents Neumann data corresponding to the sinusoidal injection current with an angular frequency ω, u is the induced time-harmonic voltage inside Ω, images, images is the double-layer potential given by

8.2 8.2

and images is the single-layer potential given by

8.3 8.3

When the Neumann data g and Dirichlet data f are available along the boundary ∂Ω, the inverse problem is to estimate the anomaly D from knowledge of the right-hand side of the identity (8.1). Owing to the expression in the sensitivity part in (8.1) containing location information of D, the formula provides useful information in estimating the anomaly D.

8.1 Harmonic Analysis and Potential Theory

8.1.1 Layer Potentials and Boundary Value Problems for Laplace Equation

For simplicity, we will restrict ourselves to three-dimensional cases, although all the arguments in this chapter work for general dimensions with minor modifications. We also assume that both D and Ω are Lipschitz domains and images. The boundary value problem of the Laplace equation can be solved by single- or double-layer potentials with a surface potential density. The reason is that a solution images of the Laplace equation images in Ω can be expressed as

8.4 8.4

where

images

Here, the relation between the Dirichlet data f and Neumann data g is dictated by

8.5 8.5

To see the relation more clearly, define a trace operator

8.6 8.6

The operator images in (8.6) appears to be the same as images in (8.2), but there exists a clear difference between them due to the singular kernel images at r = r′. The following theorem explains how the double-layer potential jumps across ∂Ω due to its singular kernel.


Theorem 8.1.1
The trace operator images is bounded on images. (When ∂Ω is a C1 domain, images is a compact operator.) For images, the following trace formulas hold almost everywhere on ∂Ω (and limit in images sense):

8.7 8.7

8.8 8.8

8.9 8.9

where I is the identity operator on images and images is the dual operator of images.

Here, the term “almost everywhere” on ∂Ω means all points except a set of measure zero in ∂Ω. For detailed explanations on these issues in measure theory, see section 4.5. The proof of the boundedness of the trace operator images in Theorem 8.1.1 for the Lipschitz domain Ω requires a deep knowledge on the harmonic analysis (Coifman et al. 1982, David and Journé 1984), while the proof in the C2 domain Ω is a lot simpler (Folland 1976). To prove Theorem 8.1.1, we need to use the following lemma.


Lemma 8.1.2
Denoting

images

we have

images


 


Proof.
For ease of explanation, we restrict ourselves to the case of the C1 domain Ω. For images, we have

images

If images, there exists a ball images (as shown in Figure 8.1) such that images and application of the divergence theorem over the region images leads to

8.10 8.10

Direct calculation over the sphere images yields

images

Finally, let images (see Figure 8.1b). Denoting images, we have

images


Figure 8.1 Diagrams showing (a) images and images and (b) images. The ratio images images is about half for small images

8.1

Now, we are ready to prove the trace formula in Theorem 8.1.1. We will only prove the trace formula (8.7) under the assumption that ∂Ω is C2 and images. For images,

images

From Lemma 8.1.2, images and images and, therefore,

8.11 8.11

Since images (this property is not necessary for the proof of (8.7), and see Remark 8.1.3), ϕ(r) − ϕ(r′) = O(|rr′|) and

8.12 8.12

Since images as a function of r′ is integrable over ∂Ω, it follows from the Lebesgue dominated convergence theorem and Lemma 8.1.2 that

8.13 8.13

From (8.13) and (8.11), we obtain

images


Remark 8.1.3
The limit (8.13) via the Lebesgue dominated convergence theorem (LDCT) holds true even for the Lipschitz domain Ω and images. To apply the LDCT, we use some estimate using the Hardy–Littlewood maximal function to replace the estimate of (8.12). To understand it simply, we assume that images is the domain above the graph images. For images, there is a positive constant C depending only on images so that

images

where ψr(r′) = ϕ(r′) − ϕ(r) and images for images.

 


Theorem 8.1.4
The following operators are all invertible:

8.14 8.14

8.15 8.15

8.16 8.16

8.17 8.17


 


Proof.
We only prove that images is invertible. Recall the definition of the null space N and the range R of an operator:

images

It is well known in functional analysis (see Rudin 1973, theorem 4.12) that

8.18 8.18

We will prove that images implies ϕ = 0. From (8.9),

images

where images and images denote the limits of a function f from outside and inside of Ω, respectively. If images, then images satisfies

images

From the uniqueness (up to a constant) of the exterior Neumann boundary value problem, images in images and images in images because images for |r| = ∞. Hence images satisfies the interior Dirichlet boundary value problem

images

From the maximum principle, images in Ω and, therefore, images in images. As a result, we have

images

and hence,

images

From (8.18), images and, therefore, the closure of images is images.
Now we will prove images by showing that the range of images is closed. According to the Banach closed range theorem (Rudin 1973, p. 96), it suffices to show that images has a closed range. We need to prove that, if images is the limit of images, then there exists images such that images.
Case (i). Consider the case where images. Owing to the weak compactness (Evans 2010), there exists a subsequence images weakly in images. Then, we have

images

Hence, images.
Case (ii). It remains to prove the case where images. We may assume that images. Denoting images, we have

8.19 8.19

Since images, there exists a subsequence images such that images weakly in images.
We repeat the previous argument to get

images

Hence images and images weakly on ∂Ω. Verchota (1984) obtained the following remarkable contradiction, which indicates that case (ii) is not possible.

images

Here, we have used the estimate in Lemma 8.15 (see below), (8.19) and the fact that, if images weakly on ∂Ω, then images
From (i) and (ii), we obtain images. Hence, to prove its invertibility, it remains to prove that images is one-to-one. It is sufficient to prove that images has a dense range on images. For the Lipschitz domain Ω, we may use a sequence images of C2 domains such that images. We know that for C2 boundary images, images is a compact operator and the Fredholm alternative theorem can be applied to get images. With the aid of this property, we can obtain that the closure of images is images. (Please refer to Verchota (1984) for the details of the proof.) This completes the proof of the invertibility of images. Hence, we also get the invertibility of images. To prove the invertibility of images, we may repeat similar arguments.

 


Lemma 8.1.5 (Verchota 1984)
Let Ω be a bounded Lipschitz domain in images with a connected boundary. Then, for all images, we have

8.20 8.20

8.21 8.21

where C depends only on the Lipschitz constant for Ω.

 


Proof.
Let images and denote

8.22 8.22

We decompose images on ∂Ω into

images

The proof is based on the following Rellich identity.
(Rellich identity) Let images be a vector field satisfying images on ∂Ω. Then, we have the following identity:

8.23 8.23

where images is

images

The identity (8.23) follows from

8.24 8.24

which can be obtained by applying the Gauss divergence to the following identity:

images

The Rellich identity (8.23) provides the following estimates:

images

where the constant C depends on images and images. Since images, we obtain

8.25 8.25

8.26 8.26

8.27 8.27

where the constant C is independent of u and ϕ. Setting

images

(the average), the term images can be estimated by

8.28 8.28

where the constant C is independent of u and ϕ. Here, we have used the Poincaré inequality

images

Combining all the estimates (8.25)–(8.28) with the Hölder inequality, we obtain

8.29 8.29

where the constant C is independent of u and ϕ. This completes the proof.

We briefly summarize the layer potential method for the boundary value problems (BVP) of the Laplace equation on the Lipschitz domain Ω (Fabes et al. 1978). With the aid of the layer potential method, solving the Neumann BVP can be converted into the invertibility of images. Since it is invertible, the potential

images

satisfies

images

8.1.2 Regularity for Solution of Elliptic Equation along Boundary of Inhomogeneity

In this section, we study the regularity of solutions of elliptic equations on a Lipschitz interface based on the work by Escauriaza and Seo (1993). Throughout this section, let images be the unit ball and let D be a Lipschitz domain with a connected boundary contained in B1/2 where Br denotes the ball with radius r and center at the origin. We consider a weak solution images for the elliptic equation

8.30 8.30

where A0 and AD are positive constant matrices.

Denote by F0(r) and FD(r), respectively, the fundamental solutions of the constant-coefficient elliptic operators

images

We define the corresponding single-layer potentials images and images as

images

The corresponding trace operators are defined as, for r ∈ ∂D,

images

For ϕ ∈ H1(B), we define the interior and exterior non-tangential maximal functions of ϕ at r ∈ ∂D, respectively, as

images

We write

images

We have the following regularity result for a solution images of (8.30).


Theorem 8.1.6 (Escauriaza and Seo 1993)
Suppose ADA0 is either a positive or negative definite matrix. If images is a weak solution to (8.30), then

images

where the constant C depends only on the Lipschitz character of D, A0, AD and ADA0.

 


Theorem 8.1.7
Under the assumptions on Theorem 8.1.6, the mapping

images

defined by

images

is invertible.

We will prove Theorem 8.1.6 assuming that Theorem 8.1.7 has already been proved. Take images with ϕ = 1 on B3/5, and ϕ = 0 outside B4/5. Then, uϕ satisfies

images

Introducing the Newtonian potential

images

we have

images

Since images, it is easy to see that images. Let

images

According to Theorem 8.1.7,

8.31 8.31

Define

images

From (8.31), w satisfies

images

and we must have w = 0 in images from the maximum principle, since w(r) = O(|r|−1) at infinity. Hence, we have the following representation formula:

images

The theorem follows from the property of the singular integral on the Lipschitz domain.

The main step in the proof of Theorem 8.1.7 is the following estimate.


Lemma 8.1.8
Under the assumption of Theorem 8.1.7, there exists a positive constant C depending only on the Lipschitz character of D, A0, AD and ADA0 such that, for (f, g) ∈ L2(∂D) × L2(∂D),

images


 


Proof.
After a linear change of coordinates, we may assume that A0 = I and AD = A, where I denotes the identity matrix. From the assumptions, either AI ≥ αI or IA ≥ αI for some α > 0. We only consider the case where AI ≥ αI for α > 0. Denote

images

and

8.32 8.32

Then, u satisfies

images

There exists C depending on the Lipschitz character of ∂D, A and α such that

8.33 8.33

To prove (8.33), we will derive Rellich-type identities as in the proof of Lemma 8.1.5. We choose a vector field images with images on ∂D, where C1 depends only on the Lipschitz character of D. Then,

8.34 8.34

8.35 8.35

Integrating (8.34) over D and applying the divergence theorem, we get

8.36 8.36

Using the orthonormal basis {n, t1, t2}, we can decompose

images

and

images

Applying the above identities to (8.36), we obtain

8.37 8.37

Similarly, (8.35) for u leads to

8.38 8.38

We can rewrite the last equality as

images

From the transmission conditions (8.32), we can rewrite the last equality in terms of the gradient of u+, ϕ1 and ϕ2 on ∂D, obtaining

8.39 8.39

Subtracting (8.39) from (8.37), we have

8.40 8.40

From the orthonormality of the linear base {n, t1, t2}, we have

images

for a positive constant C depending only on A and α. From (8.40) with the above estimate, we have

images

The above estimate together with a similar estimate for images give the estimate (8.33). The proof of Lemma 8.1.8 follows from the estimate (8.33) and Lemma 8.1.5.

 


Theorem 8.1.9
Under the assumption of Theorem 8.1.7, there exists a positive constant C depending only on the Lipschitz character of D, AD and A0 such that, given images, there exists a function u satisfying

8.41 8.41

8.42 8.42

8.43 8.43

8.44 8.44

8.45 8.45

Moreover, u can be represented as

images


 


Proof.
With a linear change of the coordinate system, we may assume that A0 = I. Denote AD = A. From the Lax–Milgram theorem, for each r > 1, there is a unique images such that

images

In particular,

images

Hence, we have

images

Here, images means that there exists a constant C depending only on the Lipschitz character of D, AD and A0 such that Φ ≤ CΨ. From the trace theorem, we obtain

images

From the Sobolev inequality, we have

images

Using a small constant images and Jenson's inequality, we get

images

and, therefore,

images

where the constant C is independent of r. Therefore, we can choose a sequence images such that images weakly. Clearly, this u satisfies (8.42)–(8.44). From the standard Schauder interior estimate, we have

images

From Theorem 8.1.4 by Verchota (1984), we can find f, gL2(∂D) such that

images

From the maximum principle, we have

images

Hence,

images

This completes the proof of Theorem 8.1.9.

 


Proof of Theorem 8.1.7.
To prove that the operator images is one-to-one, let f, gL2(∂D) satisfy images and images on ∂D. Then, the function u defined as images in D and images in images lies in images and is a weak solution of Lu = 0 in images. Thus u must be identically zero by the maximum principle. Hence images in images and images in images. From the jump relations,

images

Therefore, f must be zero on ∂D. Similar arguments give g = 0 on ∂D.
Next, we will prove that images has a closed range. As in Theorem 8.1.4, we first assume that

images

If images, we may then assume that fjf weakly for some fL2(∂D) and gjg weakly for some gL2(∂D) and, therefore, we can easily conclude that images and images.
If images, we may assume images, images and images. Since images is one-to-one, we may assume that fj → 0 weakly in L2(∂D) and gj → 0 weakly in L2(∂D). Since images and images are compact operators from L2(∂D) to L2(∂D), images and images converge strongly to zero in L2(∂D). But, since

images

there is a contradiction.
Now it remains to prove that images has a dense range. As in Verchota (1984), approximation of D by smooth domains and the estimate in Lemma 8.1.8 will give that the operator in Theorem 8.1.7 has a dense range, if the range of this operator is dense when D is a smooth domain. Let ϕ1 and ϕ2 in images be given. From Theorem 8.1.9, we can find f1 and g in L2(∂D) such that

images

where images. From Verchota (1984), we can find fL2(∂D) such that

images

Clearly, images and images has a dense range when D is smooth. This completes the proof of Theorem 8.1.7.

8.2 Anomaly Estimation using EIT

In this section, we focus our attention on the estimation of the sizes of anomalies with different conductivity values compared with the background tissues. We describe how to estimate their size using the relationship between injection currents and measured boundary voltages. There are many potential applications where the locations and sizes of anomalies or changes in them with time or space are of primary concern. They include monitoring of impedance-related physiological events, breast cancer detection, bubble detection in two-phase flow and others in medicine and non-destructive testing.

Let images denote an electrically conducting medium and let the anomalies occupy a region D contained in the homogeneous medium Ω. Then, the conductivity distribution σ can be written as

8.46 8.46

where σ0 is a positive constant (which will be assumed to be 1 for simplicity) and μ is a constant such that − 1 < μ ≠ 0 < ∞. Physically, σ0 is the conductivity of the homogeneous background images and σ0μ: = σD − σ0, where σD is the conductivity of the anomaly D. A high contrast in conductivity occurs at the interface ∂D between the anomaly D and the background images.

The goal is to develop an algorithm for extracting quantitative core information about D from the relationship between the applied Neumann data images and the measured Dirichlet data images. Here u is the induced potential due to the Neumann data g, and it is determined by solving the Neumann problem:

8.47 8.47

Throughout this section, images, where u0 is the potential satisfying

8.48 8.48


Theorem 8.2.1 (Kang and Seo 1996)
The function images for images can be expressed as

8.49 8.49

where F(r) = − 1/(4π|r|). The difference images can be expressed as

8.50 8.50


 


Proof.
Using the fact that images in the distribution sense, we have

images

for all images. We now use the refraction condition of u along ∂D to get

8.51 8.51

These prove (8.49). The expression (8.50) follows from (8.49) and

8.52 8.52


This theorem plays an important role in extracting location information about D. This section considers non-iterative anomaly estimation algorithms for searching its location and estimating its size.

8.2.1 Size Estimation Method

Kang et al. (1997) derived that, with the special Neumann data g = a · n where a is a unit constant vector, the volume of D can be estimated by

8.53 8.53

where u0 is the corresponding solution of (8.47) with the homogeneous conductivity distribution. Alessandrini et al. (2000) provided a careful analysis on the bound of the size of inclusions for a quite general g and conductivity distribution. In this section, we will explain the results of Alessandrini et al. (2000) in detail.

Before presenting an analysis of size estimation, we begin by explaining the algorithm to estimate the total size of anomalies proposed by Kwon and Seo (2001). The total size estimation of anomalies images uses the projection current g = a · n, where a is a unit constant vector. We may assume that Ω contains the origin. Define the scaled domain images for a scaling factor t > 0. Let vt be the solution of the problem

images

The following lemma provides a way to compute |D|.


Lemma 8.2.2 (Kwon and Seo 2001)
There exists a unique t0, 0 < t0 < 1, so that

images


 


Proof.
Let images as a function of t defined in the interval (0, 1). If t1 < t2, it follows from integration by parts that

images

These identities give the monotonicity of η(t):

images

Since images, a similar monotonicity argument leads to the following inequalities;

images

images

Since η(t) is continuous, there exists a unique t0 so that images.

With the aid of the above lemma, Kwon and Seo (2001) developed the following method of finding the total size of multiple anomalies.

  • Suppose that images. With an applied current g = a · n, where a is a unit constant vector, choose the unique t0, 0 < t0 < R, so that

images

  • Then, the size of the ball images is a good approximation of the total size of images.

Various numerical experiments indicate that the above algorithm gives a nearly exact estimate for arbitrary multiple anomalies with a quite general conductivity distribution, as shown in Figure 8.2.

Figure 8.2 Numerical simulation for size estimation using Lemma 8.2.2 and phantom experiments for size estimation and location search. From Kwon et al. (2003). Reproduced with permission from IEEE

8.2

Next, we will provide an explanation on the background idea of the size estimation for the case where μ is small. Integrating by parts yields

images

where σ = 1 + μχD and images. By adding the above two identities, we obtain

images

According to the choice of t0,

images

If μ ≈ 0, then images and images are approximately constant, images and the above identity is possible when the volume of images is close to the total volume images.


Theorem 8.2.3 (Alessandrini et al. 2000)
Let Ω be a bounded domain in images with a connected C1 boundary such that images is connected for all d > 0. Let images for a fixed d0 > 0. Assume that the conductivity distribution is

images

where λI ≤ σ ≤ (1/λ)I for some λ > 0, and AD and A0 are constant matrices such that αIADA0 and AD ≤ μA0 for some positive constants α, μ. Then, we have

8.54 8.54

where p > 1, C1 and C2 are positive constants depending on d0, λ, Ω and images

 


Remark 8.2.4
Definitely, we can get an estimate similar to (8.54) for the case where αIA0AD and μA0AD. In this case, we can get the following result, which is similar to (8.54):

8.55 8.55

Theorem 8.2.3 can be stated in greater generality. A0 and AD are not necessarily constant matrices. We refer to Alessandrini et al. (2000) for a precise statement for conditions on A0 and AD. The proof of the estimate (8.54) relies on the results by Garofalo and Lin (1986), in which they developed an elegant theory that connects the unique continuation property for solutions of elliptic partial differential equations with the theory of Ap Muckenhoupt weights.

 


Lemma 8.2.5
Under the assumption of Theorem 8.2.3, we have

8.56 8.56


 


Proof.
Denote G = ADA0. The proof is based on the following three identities:

8.57 8.57

8.58 8.58

8.59 8.59

The identity (8.57) yields

images

From (8.57) and (8.58), we have

images

and, therefore,

images

This completes the proof.

 


Lemma 8.2.6
Under the assumption of Theorem 8.2.3, we have the following estimate for every ρ > 0:

8.60 8.60

where Cρ depends only on ρ, d0, λ, Ω and images

 


Proof.
From the three sphere inequality given by Garofalo and Lin (1986), there exist C ≥ 1 and δ ∈ (0, 1) depending on λ and d0 such that

images

where

images

Applying the Caccioppoli and Poincaré inequalities, we have

8.61 8.61

which leads to

8.62 8.62

Here, the constant C differs on each occurrence but all of the C are independent of u0 and depend only on ρ, d0, λ, Ω and images.
Let images be any two points. Note that the two points images and r′ can be joined by a polygonal arc with node points images such that |rjrj+1| = 2ρ for j = 1, 2, …, L − 1 and images. From the estimate (8.62), we have

8.63 8.63

and by induction

8.64 8.64

By covering images with balls of radius ρ using the estimate (8.64), we have

8.65 8.65

and, therefore,

8.66 8.66

It remains to derive an appropriate lower bound for W to estimate (8.60). To be precise, it suffices to prove that there exists ρ* > 0 depending only on λ, Ω, images and images such that

8.67 8.67

If (8.67) holds true, then images for ρ < ρ*, and (8.66) and (8.67) yield

8.68 8.68

If (8.68) holds true, it is obvious that the estimate on the right-hand side of (8.68) holds true for ρ > ρ*.
Hence, it remains to prove the estimates (8.67). It can be proven by showing that there exists a ρ* such that

8.69 8.69

The proof of (8.69) follows from a careful adaptation of results by Kenig et al. (2007):

8.70 8.70

where C > 0 depends on λ and the Lipschitz character of Ω only. The proof of the estimate (8.70) requires a deep knowledge of harmonic analysis when ∂Ω is only Lipschitz, while it is a lot simpler when ∂Ω is C2. For ease of explanation, we will give the proof under the assumption that ∂Ω is in C2. By the Hölder inequality and Sobolev inequality,

8.71 8.71

where C depends on Ω only. Moreover, we have

8.72 8.72

where C depends on λ and Ω only. From (8.71) and (8.72), we have

8.73 8.73

Using the standard estimate images and (8.73), we have

8.74 8.74

where C depends on λ and Ω. Hence, we obtain (8.69) by choosing a sufficiently small ρ*. This completes the proof.

Now, we will prove Theorem 8.2.3. For p > 1, we have

8.75 8.75

We can cover D with internally non-overlapping closed cubes Qj, j = 1, …, J, with diameter ρ and ρ < d0/6. Then, (8.75) yields

8.76 8.76

We will take advantage of the fact that images is a Muckenhoupt weight (Garofalo and Lin 1986):

8.77 8.77

where M and p depend only on ρ, d0, λ, Ω and images. The left term in (8.77) can be estimated by

images

From (8.76) and the above estimate, we have

8.78 8.78

By (8.60) and (8.78), we have

8.79 8.79

where images, C2 = C1Cρλ and Cρ is the constant in (8.60). From (8.79) and the left-hand side of (8.56), we have

images

This completes the proof of the right-hand side of (8.54).

8.2.2 Location Search Method

Kwon et al. (2002) developed a location search method to detect an anomaly using a pattern injection current g and boundary voltage f. We assume that the object contains a single anomaly D that is small compared with the object itself and is located away from the boundary ∂Ω. The location search algorithm is based on simple aspects of the function H(r) outside the domain Ω, which can be computed directly from the data g and f.

We choose images for some fixed constant vector a.

1. Take two observation regions Σ1 and Σ2 contained in images given by

images

2. Find two points Pi ∈ Σi(i = 1, 2) so that

images

and

images

3. Draw the corresponding plane Π1(P1) and the line Π2(P2) given by

images

4. Find the intersecting point P of the plane Π1(P1) and the line Π2(P2). Then this point P can be viewed as the location of the anomaly D.

Figure 8.3 illustrates how the location search method works. The above location search method is based on the assumption that images for some constant α. Noting that images with the injection current g = a · n, it follows from (8.50) that

8.80 8.80

where

images

We can express w as a single-layer potential images and, therefore, w is harmonic both in D and in images. Hence, we can get the following observation by the mean value property of harmonic functions in images, and the uniqueness of the interior Dirichlet problem for the Laplace equation in D by considering the limit value of w(r) to the boundary ∂D.

Figure 8.3 Relations between the location of the anomaly and the pattern of H(r) in the case of μ > 0

8.3

Observation 8.2.7 (Kwon et al. 2002)
The function w(r) in (8.80) is harmonic in images. If D = Br(r*) is a ball, w(r) satisfies

8.81 8.81

Assuming H ≈ (μα/σ0)w outside Ω and examining the sign of w in (8.81) as depicted in Figure 8.3, we have the following:

8.82 8.82


We should note that this nice observation is made under the assumption that images, that is, images inside the anomaly D is a fixed constant vector images. Hence, we need to check whether the current images generates images for some scalar α. In the special case where Ω and D are concentric balls, we can compute u explicitly via Fourier expansion.


Exercise 8.2.8
Show that if Ω and D are concentric balls, then

8.83 8.83

for some scalar α.

 


Observation 8.2.9
For ease of explanation, let σ0 = 1 and images. Let images and D = Bρ(r*), the ball centered at r* of radius ρ. Assume that images for a positive number d and that μ ≠ 0 satisfies − 1 + 1/μ0 ≤ μ ≤ μ0 for a number μ0 ≥ 1. Take an observation line Σ1: = a line parallel to a with images. Then, there exists images with images as ρ → 0, so that for the point P1 ∈ Σ1 satisfying H(P1) = 0, the plane or the line Π1(P1): = {r:a · (rP1) = 0} hits the images-neighborhood of the center r* of D.

 


Proof.
We will compare u with a new function v (which makes quantitative analysis a lot easier) defined by

8.84 8.84

where the constant c is chosen so that images. Here, the term 3μ/(3 + μ) is chosen so that v satisfies images in images, which will be explained below.
From Observation 8.2.7, we have

8.85 8.85

A straightforward calculation of (8.85) using parametric spherical coordinates centered at r* yields

images

where v+ = v|D and images. The above identities lead to the transmission condition

images

and, therefore, v satisfies the conductivity equation images in images. The Neumann data of v on images is given by

images

where E(r, r*) is defined as

images

Hence, η: = uv solves the following Neumann problem:

8.86 8.86

We will estimate that

8.87 8.87

By simple arithmetic, we can decompose E(r, r*) into the following two terms:

images

Since R = |r|, we get the following by a simple Cauchy–Schwarz inequality:

images

In order to estimate U(r, r*), consider the spherical coordinates for images and r* with θ and α as latitudes measured from the xz plane to the y axis, respectively:

images

for − π/2 ≤ θ, α ≤ π/2 and 0 ≤ η, β ≤ 2π. Denoting t: = τ/R and r: = cos(η − β), U(r, r*) is expressed as

8.88 8.88

By a tedious calculation with (8.88), we get

images

Thus, U(r;t, α, β, θ): = U(r, r*) is monotonic for − 1 ≤ r ≤ 1 for fixed t, α, β (that is, for fixed r*) and θ. To check the extremes of U(r, r*), we only need to check

images

for 0 ≤ t < 1 and − π/2 ≤ θ, α ≤ π/2. Letting s: = imagescos(θ ± α), we get

images

Then, it is easy to get |U(r, r*)| ≤ 1. Hence, we obtain the desired assertion (8.87):

images

Since images, we see that |rr*| ≥ d for all images. In addition, the fact that |μ|/(3 + μ) ≤ 1 for all − 1 < μ < ∞ gives the estimate

8.89 8.89

Under the assumption that − 1 < − 1 + 1/μ0 ≤ μ ≤ μ0 < ∞, we are ready to compare H(r) with

images

in the region images. From (8.49), we have

8.90 8.90

Therefore, by the observation that

images

we obtain the following estimate by the standard Hölder estimate of (8.90):

8.91 8.91

We claim that there exists a positive constant images so that

8.92 8.92

The proof of (8.92) is a bit technical and lengthy, so we omit its here. Conditions (8.91) and (8.92) lead to the following estimate:

8.93 8.93

Note that by using the mean value theorem for harmonic functions, we easily get

8.94 8.94

From (8.93) and (8.94), we obtain the final estimate

8.95 8.95

where images is given by

8.96 8.96

Now let images be defined as follows, which clearly satisfies images as ρ → 0:

images

where images, independent of ρ, is given by (8.96). Because there is nothing to be proved if images, we may assume that ρ < 1/C from now on.
For r ∈ Σ1 satisfying images, we have

images

Hence, by the positiveness of (rr*) · a and the definition of images, we obtain

images

On the other hand, for r ∈ Σ1 satisfying images, we have

images

Being careful of the negativeness of (rr*) · a, we similarly obtain

images

In the end, by the estimate (8.95) we have, if μ > 0,

images

Note that the sign of H(r) is exchanged if μ < 0. Therefore, the zero point P1 ∈ Σ1 of H(r) satisfies images, which completes the proof.

Although the basic idea of the algorithm is simple, several technical arguments are needed for its proof. Combining this location search algorithm with the size estimation algorithm proposed in Kwon and Seo (2001), one can select an appropriate initial guess. Figure 8.4 explains this algorithm.

Figure 8.4 Location detection by finding an intersecting point of two lines Π1(P1) and Π2(P2)

8.4

In order to test the feasibility of the location search and size estimation methods, Kwon et al. (2003) carried out phantom experiments. They used a circular phantom with 290 mm diameter as a container and filled it with NaCl solution of conductivity 0.69 S m−1. Anomalies with different conductivity values, shapes and sizes were placed inside the phantom. A total of 32 equally spaced electrodes were attached on the surface of the phantom. Using a 32-channel EIT system, they applied the algorithms to measured boundary voltage data. The circular phantom can be regarded as a unit disk images by normalizing the length scale. To demonstrate how the location search and size estimation algorithm work, they placed four insulators images into the phantom:

images

They injected a projection current images with images and measured the boundary voltage f. For the location search, they chose two observation lines:

images

They evaluated the two-dimensional version of H(r) with F replaced by images. In Figure 8.3, the left-hand plot is the graph of H(r) on Σ1 and the right-hand plot is the graph of H(r) on Σ2. They found the zero point of H(r) on Σ1 and the maximum point of |H(r)| on Σ2 as denoted by the black dots in Figure 8.3. The intersecting points were calculated as P( − 0.1620, − 0.0980), which was close to the center of mass PM( − 0.1184, − 0.0358). For the case of a single anomaly or a cluster of multiple anomalies, the intersecting point furnished meaningful location information.

For the size estimation, the estimated total size was 0.4537 compared with the true total size of 0.4311. In Figure 8.2, the corresponding disk with the size of 0.4537 centered at P( − 0.1620, − 0.0980) is drawn with a solid line and the corresponding disk with the true size centered at PM is drawn with a dotted line. The relative error of the estimated size was about 5.24%.


Remark 8.2.10
Numerous experimental results by Kwon et al. (2003) using a circular saline phantom showed the feasibility of the method for many applications in medicine and non-destructive testing. The algorithm is also fast enough for real-time monitoring of impedance-related events. The performance of the location and size estimation algorithm is not sensitive to anomaly shapes, locations and configurations. In practice, μ defined as the conductivity contrast between the background and anomaly is unknown. Note that the location search method does not depend on μ, whereas the size estimation does depend on μ.
In the case of multiple anomalies, the location search algorithm produces a point close to the center of mass of multiple anomalies. If they are widely scattered, this information may not be useful or may be misleading in some applications. However, when they form a cluster of small anomalies, this point becomes meaningful. For more detailed explanations on anomaly estimations, see Ammari and Kang (2007).

8.3 Anomaly Estimation using Planar Probe

In this section, we describe anomaly estimation techniques using a local measurement from a planar probe placed on a portion of an electrically conducting object. The detection of breast cancer using a trans-admittance scanner (TAS) is a typical example of this setting. TAS is based on the experimental findings showing that the complex conductivity values of breast tumors differ significantly from those of surrounding normal tissues (Assenheimer et al. 2001; Hartov et al. 2005; Jossinet and Schmitt 1999; Silva et al. 2000). In TAS, with one hand a patient holds a reference electrode through which a sinusoidal voltage V0sinωt is applied, while a scanning probe at the ground potential is placed on the surface of the breast. The voltage difference V0sinωt produces an electric current flowing through the breast region (see Figure 8.5). The resulting electric potential at position r = (x, y, z) and time t can be expressed as the real part of u(r) et, where the complex potential u(r) is governed by the equation images in the object, where σ and images denote the conductivity and permittivity, respectively. The scanning probe is equipped with a planar array of electrodes and we measure exit currents (Neumann data) images, which reflect the electrical properties of tissues under the scanning probe.

Figure 8.5 Configuration for breast cancer detection using TAS

8.5

The inverse problem of TAS is to detect a suspicious abnormality in a breast region underneath the probe from measured Neumann data g. One may utilize the difference gg0, where g0 is reference Neumann data measured beforehand without any anomaly inside the breast region (Ammari et al. 2004; Kim et al. 2008; Seo et al. 2004). This difference gg0 can be viewed as a kind of background subtraction, so that it makes the anomaly apparently visible. However, it may not be available in practice, and calculating g0 is not possible since the inhomogeneous complex conductivity of a specific normal breast is unknown. In such a case, we should use a frequency-difference TAS method.

8.3.1 Mathematical Formulation

Let the human body occupy a three-dimensional domain Ω with a smooth boundary ∂Ω. Let Γ and γ be portions of ∂Ω, denoting the probe plane placed on the breast and the surface of the metallic reference electrode, respectively. Through γ, we apply a sinusoidal voltage of V0sinωt with frequency f = ω/2π in the range of 50 Hz to 500 kHz. Then the corresponding complex potential uω at ω satisfies the following mixed boundary value problem:

8.97 8.97

where n is the unit outward normal vector to the boundary ∂Ω. Note that both images and images depend on ω. The scan probe Γ consists of a planar array of electrodes images and we measure the exit current gω(j) through each electrode images:

images

In the frequency-difference TAS, we apply voltage at two different frequencies, f1 = ω1/2π and f2 = ω2/2π, with 50 Hz ≤ f1 < f2 ≤ 500 kHz, and measure two sets of corresponding Neumann data images and images through Γ at the same time. We assume that there exists a region of breast tumor D beneath the probe Γ so that images changes abruptly across ∂D. The inverse problem of frequency-difference TAS is to detect the anomaly D beneath Γ from the difference between images and images.

In order for any detection algorithm to be practicable, we must take account of the following limitations.

a. Since Ω differs for each subject, the algorithm should be robust against any change in the geometry of Ω and also any change in the complex conductivity distribution outside the breast region.
b. The Neumann data gω are available only on a small surface Γ instead of the whole surface ∂Ω.
c. Since the inhomogeneous complex conductivity of the normal breast without D is unknown, it is difficult to obtain the reference Neumann data images in the absence of D.

These limitations are indispensable to a TAS model in practical situations. In the frequency-difference TAS model, we use a weighted frequency difference of Neumann data images instead of images. The weight α is approximately

images

and it is a crucial factor in anomaly detection. We should note that the simple difference images may fail to extract the anomaly owing to the complicated structure of the solution of the complex conductivity equation. We need to understand how images reflects a contrast in complex conductivity values between the anomaly D and surrounding normal tissues.

We assume that σ and images are isotropic, positive and piecewise smooth functions in images. Let uω be the images solution of (8.97). Denoting the real and imaginary parts of uω by images and images, the mixed boundary value problem (8.97) can be expressed as the following coupled system:

8.98 8.98

The measured Neumann data gω can be decomposed into

images

The solution of the coupled system (8.98) is a kind of saddle point (Borcea 2002; Cherkaev and Gibiansky 1994), and we have the following relations:

8.99 8.99

and

8.100 8.100

where we have images and images.

In order to detect a lesion D underneath the scanning probe Γ, we define a local region of interest under the probe plane Γ as shown in Figure 8.6. For simplicity, we let z be the axis normal to Γ and let the center of Γ be the origin. Hence, the probe region Γ can be approximated as a two-dimensional region images, where L is the radius of the scan probe. We set the region of interest inside the breast as a half-ball images, as shown in Figure 8.6, where BL is a ball with radius L and its center at the origin.

Figure 8.6 (a) Simplified model of the breast region with a cancerous lesion D under the scanning probe. (b) Schematic of the scanning probe in the (x, y) plane

8.6

Remark 8.3.1
In Table 8.1 we summarize the conductivity and permittivity values of normal and tumor tissues in the breast. Both σ and images have a unit of S m−1 and images, where images is the permittivity of free space and images is the relative permittivity. Note that images for a frequency f = ω/2π ≥ 50 kHz (Surowiec et al. 1988).

Table 8.1 Conductivity and permittivity values of normal and tumor breast tissues

NumberTable

For successful anomaly detection, we should carefully choose the two frequencies ω1 and ω2. One may choose f1 = ω1/2π and f2 = ω2/2π such that

8.101 8.101

We denote by u1 = v1 + ih1 and u2 = v2 + ih2 the complex potentials satisfying (8.98) at ω1 and ω2, respectively, and let images and images. The frequency-difference TAS aims to detect D from a weighted difference between g1 and g2.

Now, let us investigate the connection between u1 and u2 and whether the frequency-difference Neumann data g2 − αg1 contain any information about D. Since both σ and images depend on ω and images, σ(r, ω1) ≠ σ(r, ω2) and images. For simplicity, we denote

images

Suppose there is a cancerous lesion D inside images and the complex conductivity images changes abruptly across ∂D as in Table 8.1. To distinguish them, we denote

8.102 8.102

With the use of this notation, u1 and u2 satisfy

8.103 8.103


Remark 8.3.2
Owing to the complicated structure of (8.99) and (8.100) for the solution uω, it is quite difficult to analyze the interrelation between the complex conductivity contrast images and the Neumann data gω. The simple frequency-difference data g2g1 on Γ may fail to extract the anomaly for more general cases of complex conductivity distributions in Ω because of the complicated structure of the solution of (8.98). To be precise, the use of the weighted difference is essential when the background comprises biological materials with non-negligible frequency-dependent complex conductivity values. To explain this clearly, consider a homogeneous complex conductivity distribution in Ω, where images depends only on ω. Owing to the frequency dependence, the simple difference g2g1 is not zero, while g2 − αg1 = 0. Hence, any reconstruction method using g2g1 always produces artifacts because g2g1 does not eliminate modeling errors. See (8.113) for an approximation of g2g1 in the presence of an anomaly D.

 


Remark 8.3.3
Here, we do not consider effects of contact impedances along electrode–skin interfaces. For details about contact impedances, please see Somersalo et al. (1992), Hyvonen (2004) and other publications cited therein. In TAS, we may adopt a skin preparation procedure and electrode gels to reduce contact impedances. Since we cannot expect complete removal of contact impedances, however, we need to investigate how the exit currents are affected by the contact impedances of a planar array of electrodes that are kept at the ground potential. The contact impedance of each electrode leads to a voltage drop across it and therefore the voltage beneath the electrode–skin interface layer would be slightly different from zero. In other words, when contact impedances are not negligible, the surface area in contact with Γ cannot be regarded as an equipotential surface any more, and this will result in some changes in exit currents. Future studies are needed to estimate how the contact impedance affects the weighted difference of the Neumann data. We should also investigate experimental techniques, including choice of frequencies to minimize their effects.

The next observation explains why we should use a weighted difference g2 − αg1 instead of g2g1.


Observation 8.3.4
Denoting

images

it follows from a direct computation that u2u1 satisfies

8.104 8.104

For the detection of D, we use the following weighted difference:

images

where α = η|Γ. If images in (8.104), then u1 = u2 in Ω and g2 − αg1 = 0 on Γ. In other words, if images in images, it is impossible to detect D from g2 − αg1 = 0 regardless of the contrasts in σ and images across ∂D. Any useful information on D could be found from non-zero g2 − αg1 on Γ when images is large alongD.
For chosen frequencies ω1 and ω2, we can assume that σ and images are approximately constant in the normal breast region images and also in the cancerous region D. Hence, if η changes abruptly across ∂D, we roughly have

images

and therefore the term images in (8.104) is supported onD in the breast region images. This explains why the difference g2 − αg1 on Γ can provide information of ∂D. We note that the inner product images is to be interpreted in a suitable distributional sense if the coefficients jump atD.

8.3.2 Representation Formula

Observation 8.3.4 in the previous section roughly explains how D is related to g2 − αg1. In this section, the observation will be justified rigorously in a simplified model. We assume that σj, n, σj, c, images and images are constants. According to Table 8.1, the change in conductivity due to the change in frequency is small, so we assume that

8.105 8.105

Since the breast region of interest is relatively small compared with the entire body Ω, we may assume that Ω is the lower half-space images and γ = ∞.

Suppose that vj and hj are H1-solutions of the following coupled system for j = 1, 2:

8.106 8.106

Let uj = vj + ihj. Then V0(1 − uj) can be viewed as a solution of (8.103) with images and γ = ∞.

Let us introduce a key representation formula explaining the relationship between D and the weighted difference g2 − αg1. For each images, we define

images

where images is the reflection point of r′ with respect to the plane {z = 0} and φ(r, · ) is the images-solution of the following PDE:

images

The following theorem explains an explicit relation between D and images.


Theorem 8.3.5 (Kim et al. 2008)
The imaginary part of the weighted difference g2 − αg1 satisfies the following (for r ∈ Γ):

8.107 8.107

where

images

and

images


Now, let us derive a constructive formula extracting D from the representation formula (8.107) under some reasonable assumptions. We assume that

8.108 8.108

where C1 is a positive constant, Bδ is a ball with radius δ and center images, and images. Suppose we choose ω1/2π ≈ 50 Hz and ω2/2π ≈ 100 kHz. Then the experimental data in Remark 8.3.1 shows that

images

Hence, in practice, we can assume that

8.109 8.109

Based on the experimental data in Remark 8.3.1, we assume that

8.110 8.110

where κ1 and κ2 are positive constants less than images and κ3 is a positive constant less than 10. Taking advantage of these, we can simplify the representation formula (8.107).


Theorem 8.3.6
Under the assumptions (8.108) and (8.110), the imaginary part of the weighted frequency difference g2 − αg1 can be expressed as

8.111 8.111

where

images

and the error term Error(r) is estimated by

8.112 8.112

Here, images is a polynomial function of order n such that images and its coefficients depend only on κj, j = 1, 2, 3.

 


Remark 8.3.7
According to Theorem 8.3.6,

images

Hence, even if images and images are quite different, we cannot extract any information on D when

images

On the other hand, even if images, we can extract information on D whenever

images


 


Remark 8.3.8
Based on (8.111), we can derive the following simple approximate formula for the reconstruction of D:

8.113 8.113

where U is the solution of (8.106) in the absence of any anomaly at images. Note that the difference g2g1 can be approximated by

8.114 8.114

and therefore any detection algorithm using the above approximation will be disturbed by the term images.

 


Remark 8.3.9
The reconstruction algorithm is based on the approximation formula (8.113). In practice, we may not have a priori knowledge of the background conductivities. In that case, α is unknown. But α can be evaluated approximately by the ratio of the measured Neumann data as follows:

8.115 8.115

Hence, we may choose images.

We can prove the identity (8.115) for a bounded domain Ω. Using u1|γ = u2|γ = V0, we have

images

The identity (8.115) follows from the fact that

images

References

Alessandrini G, Rosset E and Seo JK 2000 Optimal size estimates for the inverse conductivity problem with one measurement. Proc. Am. Math. Soc. 128, 53–64.

Ammari H and Kang H 2007 Polarization and Moment Tensors: With Applications to Inverse Problems and Effective Medium Theory. Applied Mathematical Sciences, no. 162. Springer, New York.

Ammari H, Kwon O, Seo JK and Woo EJ 2004 T-scan electrical impedance imaging system for anomaly detection. SIAM J. Appl. Math. 65, 252–266.

Assenheimer M, Laver-Moskovitz O, Malonek D, Manor D, Nahliel U, Nitzan R and Saad A 2001 The T-scan technology: electrical impedance as a diagnostic tool for breast cancer detection. Physiol. Meas. 22, 1–8.

Borcea L 2002 EIT electrical impedance tomography. Inv. Prob., 18(6), R99–R136.

Cherkaev AV and Gibiansky LV 1994 Variational principles for complex conductivity, viscoelasticity and similar problems in media with complex moduli. J. Math. Phys. 35(1), 127–145.

Coifman RR, McIntosh A and Meyer Y 1982 L'intégrale de Cauchy definit un opérateur bournée sur L2 pour courbes lipschitziennes. Ann. Math. 116, 361–387.

David G and Journé JL 1984 A boundedness criterion for generalized Calderón–Zygmund operators. Ann. Math. 120, 371–397.

Escauriaza L and Seo JK 1993 Regularity properties of solutions to transmission problems. Trans. Am. Math. Soc. 338, 405–430.

Evans LC 2010 Partial Differential Equations. Graduate Studies in Mathematics, vol. 19. American Mathematical Society, Providence, RI.

Fabes E, Jodeit M and Riviére N 1978 Potential techniques for boundary value problems on C1 domains. Acta Math. 141, 165–186.

Folland G 1976 Introduction to Partial Differential Equations. Princeton University Press, Princeton, NJ.

Garofalo N and Lin F 1986 Monotonicity properties of variational integrals, Ap weights and unique continuation. Indiana Univ. Math. J. 35, 245–268.

Hartov A, Soni N and Halter R 2005 Breast cancer screening with electrical impedance tomography. In Electrical Impedance Tomography: Methods, History and Applications, ed. DS Holder, pp. 167–185. IOP Publishing, Bristol.

Hyvonen N 2004 Complete electrode model of electric impedance tomography: approximation properties and characterization of inclusions. SIAM J. Appl. Math. 64, 902–931.

Jossinet J and Schmitt M 1999 A review of parameters for the bioelectrical characterization of breast tissue. Ann. N.Y. Acad. Sci. 873, 30–41.

Kang H and Seo JK 1996 Layer potential technique for the inverse conductivity problem. Inv. Prob. 12, 267–278.

Kang H, Seo JK and Sheen D 1997 The inverse conductivity problem with one measurement: stability and estimation of size. SIAM J. Math. Anal. 28, 1389–1405.

Kenig C, Sjostrand J and Uhlmann G 2007 The Calderon problem with partial data. Ann. Math. 165, 567–591.

Kim S, Lee J, Seo JK, Woo EJ and Zribi H 2008 Multi-frequency trans-admittance scanner: mathematical framework and feasibility. SIAM J. Appl. Math. 69, 22–36.

Kwon O and Seo JK 2001 Total size estimation and identification of multiple anomalies in the inverse electrical impedance tomography. Inv. Prob. 17, 59–75.

Kwon O, Seo JK and Yoon JR 2002 A real-time algorithm for the location search of discontinuous conductivities with one measurement. Commun. Pure Appl. Math. 55, 1–29.

Kwon O, Yoon JR, Seo JK, Woo EJ and Cho YG 2003 Estimation of anomaly location and size using electrical impedance tomography. IEEE Trans. Biomed. Eng. 50, 89–96.

Rudin W 1973 Functional Analysis. McGraw-Hill, New York.

Seo JK, Kwon O, Ammari H and Woo EJ 2004 Mathematical framework and anomaly estimation algorithm for breast cancer detection: electrical impedance technique using TS2000 configuration. IEEE Trans. Biomed. Eng. 51(11), 1898–1906.

Silva JE, Marques JP and Jossinet J 2000 Classification of breast tissue by electrical impedance spectroscopy. Med. Biol. Eng. Comput. 38, 26–30.

Somersalo E, Cheney M and Isaacson D 1992 Existence and uniqueness for electrode models for electric current computed tomography. SIAM J. Appl. Math. 52, 1023–1040.

Surowiec AJ, Stuchly SS, Barr JR and Swarup A 1988 Dielectric properties of breast carcinoma and the surrounding tissues. IEEE Trans. Biomed. Eng. 35, 257–263.

Verchota G 1984 Layer potentials and boundary value problems for Laplace's equation in Lipschitz domains. J. Funct. Anal. 59, 572–611.

Further Reading

Adler A, Arnold JH, Bayford R, Borsic A, Brown B, Dixon P, Faes TJC, Frerichs I, Gagnon H, Gärber Y, Grychtol B, Hahn G, Lionheart WRB, Malik A, Patterson RP, Stocks J, Tizzard A, Weiler N and Wolf GK 2009 GREIT: a unified approach to 2D linear EIT reconstruction of lung images. Physiol. Meas. 30, S35–S55.

Alessandrini G and Magnanini R 1992 The index of isolated critical points and solutions of elliptic equations in the plane. Ann. Scu. Norm. Sup. Pisa Cl. Sci. 19, 567–589.

Alessandrini G, Isakov V and Powell J 1995 Local uniqueness in the inverse problemwith one measurement. Trans. Am. Math. Soc. 347, 3031–3041.

Ammari H and Seo JK 2003 An accurate formula for the reconstruction of conductivity inhomogeneity. Adv. Appl. Math. 30, 679–705.

Ammari H, Moskow S and Vogelius MS 2003 Boundary integral formulae for the reconstruction of electric and electromagnetic inhomogeneities of small volume. ESAIM: Control Optim. Calc. Var. 9, 49–66.

Astala K and Päivärinta L 2006 Calderon's inverse conductivity problem in the plane. Ann. Math. 163, 265–299.

Barber DC and Brown BH 1984 Applied potential tomography. J. Phys. Sci. Instrum. 17 723–733.

Bellout H and Friedman A 1988 Identification problem in potential theory. Arch. Rat. Mech. Anal. 101, 143–160.

Bellout H, Friedman A and Isakov V 1992 Inverse problem in potential theory. Trans. Am. Math. Soc. 332, 271–296.

Berenstein C and Tarabusi EC 1991 Inversion formulas for the k-dimensional Radon transform in real hyperbolic spaces. Duke Math. J. 62, 1–9.

Boone K, Barber D and Brown B 1997 Imaging with electricity: report of the European Concerted Action on Impedance Tomography. J. Med. Eng. Technol. 21(6), 201–202.

Brown R and Uhlmann G 1997 Uniqueness in the inverse conductivity problem with less regular conductivities in two dimensions. Commun. Part. Differ. Eqns 22, 1009–1027.

Brown BH, Barber DC and Seagar AD 1985 Applied potential tomography: possible clinical applications. Clin. Phys. Physiol. Meas. 6, 109–121.

Brühl M and Hanke M 2000 Numerical implementation of two non-iterative methods for locating inclusions by impedance tomography. Inv. Prob. 16, 1029–1042.

Bryan K 1991 Numerical recovery of certain discontinuous electrical conductivities. Inv. Prob. 7, 827–840.

Calderón AP 1980 On an inverse boundary value problem. In Seminar on Numerical Analysis and its Applications to Continuum Physics, pp. 65–73. Sociedade Brasileira de Matemática, Rio de Janeiro.

Cedio-Fengya DJ, Moskow S and Vogelius M 1998 Identification of conductivity imperfections of small parameter by boundary measurements. Continuous dependence and computational reconstruction. Inv. Prob. 14, 553–595.

Cheney M, Isaacson D, Newell J, Goble J and Simske S 1990 NOSER: an algorithm for solving the inverse conductivity problem. Int. J. Imag. Syst. Technol. 2, 66–75.

Cheney M, Isaacson D and Newell JC 1999 Electrical impedance tomography. SIAM Rev. 41, 85–101.

Cherepenin V, Karpov A, Korjenevsky A, Kornienko V, Mazaletskaya A, Mazourov D and Meister J 2001 A 3D electrical impedance tomography (EIT) system for breast cancer detection. Physiol. Meas. 22, 9–18.

Cherepenin V, Karpov A, Korjenevsky A, Kornienko V, Kultiasov Y, Ochapkin M, Trochanova O and Meister J 2002 Three-dimensional EIT imaging of breast tissues: system design and clinical testing. IEEE Trans. Med. Imag. 21, 662–667.

Cohen-Bacrie C and Guardo R 1997 Regularized reconstruction in electrical impedance tomography using a variance uniformization constraint. IEEE Trans. Med. Imag. 16(5), 562–571.

Colton D and Kress R 1998 Inverse Acoustic and Electromagnetic Scattering Theory, 2nd edn. Springer, Berlin.

Cook RD, Saulnier GJ, Gisser DG, Goble JG, Newell JC and Isaacson D 1994 ACT3: a high-speed, high-precision electrical impedance tomography. IEEE Trans. Biomed. Eng. 41, 713–722.

Dobson D and Santosa F 1994 An image-enhancement technique for electrical impedance tomography. Inv. Prob. 10, 317–334.

Escauriaza L, Fabes E and Verchota G 1992 On a regularity thoerem for weak solutions to transmission problems with internal Lipschitz boundaries. Proc. Am. Math. Soc. 115, 1069–1076.

Fabes E, Sand M and Seo JK 1992 The spectral radius of the classical layer potentials on convex domains. IMA Vol. Math. Appl. 42, 129–137.

Fabes E, Kang H and Seo JK 1999 Inverse conductivity problem: error estimates and approximate identification for perturbed disks. SIAM J. Math. Anal. 30, 699–720.

Feldman J and Uhlmann G 2003 Inverse Problems, Lecture Note. See http://www.math.ubc.ca/~feldman/ibook/.

Franco S 2002 Design with Operational Amplifiers and Analog Integrated Circuits, 3rd edn. McGraw-Hill, New York.

Friedman A and Isakov V 1989 On the uniqueness in the inverse conductivity problem with one measurement. Indiana Univ. Math. J. 38, 563–579.

Friedman A and Vogelius MS 1989 Identification of small inhomogeneities of extreme conductivity by boundary measurements: a theorem on continuous dependence. Arch. Rat. Mech. Anal. 105, 299–326.

Fuks LF, Cheney M, Isaacson D, Gisser DG and Newell JC 1991 Detection and imaging of electric conductivity and permittivity at low frequency. IEEE Trans. Biomed. Eng. 3, 1106–1110.

Gabriel C, Gabriel S and Corthout E 1996 The dielectric properties of biological tissues: I. Literature survey. Phys. Med. Biol. 41, 2231–2249.

Gabriel S, Lau RW and Gabriel C 1996 The dielectric properties of biological tissues: II. Measurements in the frequency range 10 Hz to 20 GHz. Phys. Med. Biol. 41, 2251–2269.

Geddes LA and Baker LE 1967 The specific resistance of biological material: a compendium of data for the biomedical engineer and physiologist. Med. Biol. Eng. 5, 271–293.

Giaquinta M 1983 Multiple Integrals in the Calculus of Variations and Non-Linear Elliptic Systems. Princeton University Press, Princeton, NJ.

Gilbarg D and Trudinger N 1998 Elliptic Partial Differential Equations of Second Order. Springer, Berlin.

Gisser DG, Isaacson D and Newell JC 1988 Theory and performance of an adaptive current tomography system. Clin. Phys. Physiol. Meas. 9 (Suppl. A), 35–41.

Gisser DG, Isaacson D and Newell JC 1990 Electric current computed tomography and eigenvalues. SIAM J. Appl. Math. 50, 1623–1634.

Grimnes S and Martinsen OG Bioimpedance and Bioelectricity Basics. Academic Press, London.

Grisvard P 1985 Elliptic Problems in Nonsmooth Domains. Monographs and Studies in Mathematics, no. 24. Pitman, Boston, MA.

Henderson RP and Webster JG 1978 An impedance camera for spatially specific measurements of the thorax. IEEE Trans. Biomed. Eng., 25, 250–254.

Hettlich F and Rundell W 1998 The determination of a discontinuity in a conductivity from a single boundary measurement. Inv. Prob. 14, 67–82.

Holder D (ed.) 2005 Electrical Impedance Tomography: Methods, History and Applications. IOP Publishing, Bristol.

Hua P, Tompkins W and Webster J 1988 A regularized electrical impedance tomography reconstruction algorithm. Clin. Phys. Physiol. Meas. 9, 137–141.

Hyaric AL and Pidcock MK 2001 An image reconstruction algorithm for three-dimensional electrical impedance tomography. IEEE Trans. Biomed. Eng. 48(2), 230–235.

Ikehata M 2000 On reconstruction in the inverse conductivity problem with one measurement. Inv. Prob. 16, 785–793.

Isaacson D 1986 Distinguishability of conductivities by electric current computed tomography. IEEE Trans. Med. Imag. 5(2), 91–95.

Isaacson D and Cheney M 1991 Effects of measurement precision and finite numbers of electrodes on linear impedance imaging algorithms. SIAM J. Appl. Math. 51 1705–1731.

Isaacson D and Cheney M 1996 Process for producing optimal current patterns for electrical impedance tomography. US Patent 5588429, 31 December.

Isaacson D and Isaacson E 1989 Comment on Calderon's paper: “On an inverse boundary value problem”. Math. Comput. 52, 553–559.

Isakov V 1988 On uniqueness of recovery of a discontinuous conductivity coefficient. Commun. Pure Appl. Math. 41, 856–877.

Isakov V 1998 Inverse Problems for Partial Differential Equations. Applied Mathematical Sciences, no. 127. Springer, New York.

Lieb EH and Loss M 2001 Analysis, 2nd edn. Graduate Studies in Mathematics, vol. 14. American Mathematical Society, Providence, RI.

Kao T, Newell JC, Saulnier GJ and Isaacson D 2003 Distinguishability of inhomogeneities using planar electrode arrays and different patterns of applied excitation. Physiol. Meas. 24, 403–411.

Kerner TE, Paulsen KD, Hartov A, Soho SK and Poplack SP 2002 Electrical impedance spectroscopy of the breast: clinical imaging results in 26 subjects. IEEE Trans. Med. Imag. 21, 638–645.

Kellogg OD 1953 Foundations of Potential Theory. Dover, New York.

Kohn R and Vogelius M 1984 Determining conductivity by boundary measurements. Commun. Pure Appl. Math. 37, 113–123.

Larson-Wiseman JL 1998 Early breast cancer detection utilizing clustered electrode arrays in impedance imaging. PhD Thesis, Rensselaer Polytechnic Institute, Troy, NY.

Lionheart W, Polydorides W and Borsic A 2005 The reconstruction problem. In Electrical Impedance Tomography: Methods, History and Applications, ed. DS Holder. IOP Publishing, Bristol.

Liu N, Saulnier GJ, Newell JC, Isaacson D and Kao TJ 2005 ACT4: a high-precision, multi-frequency electrical impedance tomography. In Proc. Conf. on Biomedical Applications of Electrical Impedance Tomography, University College London, 22–24 June.

Marsden JE 1974 Elementary Classical Analysis. W.H. Freeman, San Francisco.

Mast TD, Nachman A and Waag RC 1997 Focusing and imagining using eigenfunctions of the scattering operator. J. Acoust. Soc. Am. 102, 715–725.

Metherall P, Barber DC, Smallwood RH and Brown BH 1996 Three-dimensional electrical impedance tomography. Nature 380, 509–512.

Mueller JL, Isaacson D and Newell JC 1999 A reconstruction algorithm for electrical impedance tomography data collected on rectangular electrode arrays. IEEE Trans. Biomed. Eng. 46, 1379–1386.

Nachman A 1988 Reconstructions from boundary measurements. Ann. Math. 128, 531–577.

Nachman A 1996 Global uniqueness for a two-dimensional inverse boundary value problem. Ann. Math. 142, 71–96.

Newell JC, Gisser DG and Isaacson D 1988 An electric current tomograph. IEEE Trans. Biomed. Eng. 35, 828–833.

Oh TI, Lee J, Seo JK, Kim SW and Woo EJ 2007 Feasibility of breast cancer lesion detection using multi-frequency trans-admittance scanner (TAS) with 10 Hz to 500 kHz bandwidth. Physiol. Meas. 28, S71–S84.

Reed M and Simon B 1980 Methods of Modern Mathematical Physics I: Functional Analysis, revised and enlarged edition. Academic Press, San Diego.

Rudin W 1970 Real and complex analysis. McGraw-Hill, New York.

Santosa F and Vogelius MS 1990 A backprojection algorithm for electrical impedance imaging. SIAM J. Appl. Math. 50, 216–243.

Scholz B 2002 Towards virtual electrical breast biopsy: space-frequency MUSIC for trans-admittance data. IEEE Trans. Med. Imag. 21, 588–595.

Seo JK 1996 On the uniqueness in the inverse conductivity problem. J. Fourier Anal. Appl. 2, 227–235.

Seo JK, Lee J, Kim SW, Zribi H and Woo EJ 2008 Frequency-difference electrical impedance tomography (fdEIT): algorithm development and feasibility study. Physiol. Meas. 29, 929–944.

Stein EM and Shakarchi R 2005 Real Analysis: Measure Theory, Integration and Hilbert Spaces. Princeton University Press, Princeton, NJ.

Sylvester J and Uhlmann G 1986 A uniqueness theorem for an inverse boundary value problem in electrical prospection. Commun. Pure Appl. Math. 39, 91–112.

Sylvester J and Uhlmann G 1987 A global uniqueness theorem for an inverse boundary value problem. Ann. Math. 125, 153–169.

Sylvester J and Uhlmann G 1988 Inverse boundary value problems at the boundary—continuous dependence. Commun. Pure Appl. Math. 21, 197–221.

Tidswell AT, Gibson A, Liston A, Yerworth RJ, Bagshaw A, Wyatt J, Bayford RH and Holder DS 2001 3D electrical impedance tomography of neonatal brain activity. In Biomedical Applications of EIT, EPSRC 3rd Engineering Network Meeting, London.

Vauhkonen M, Vadasz D, Karjalainen PA, Somersalo E and Kaipio JP 1998 Tikhonov regularization and prior information in electrical impedance tomography. IEEE Trans. Med. Imag. 17(2), 285–293.

Webster J 1990 Electrical Impedance Tomography. Adam Hilger, Bristol.

Wexler A, Fry B and Neuman MR 1985 Impedance-computed tomography algorithm and system. Appl. Opt. 24, 3985–3992.

Wheeden RL and Zygmund A 1977 Measure and Integral: An Introduction to Real Analysis. Monographs and Textbooks in Pure and Applied Mathematics, vol. 43. Marcel Dekker, New York.

Wilson AJ, Milnes P, Waterworth AR, Smallwood RH and Brown BH 2001 Mk3.5: a modular, multi-frequency successor to the Mk3a EIS/EIT system. Physiol. Meas. 22, 49–54.

Woo EJ, Hua P, Webster J and Tompkins W 1993 A robust image reconstruction algorithm and its parallel implementation in electrical impedance tomography. IEEE Trans. Med. Imag. 12, 137–146.

Yorkey T, Webster J and Tompkins W 1987 Comparing reconstruction algorithms for electrical impedance tomography. IEEE Trans. Biomed. Engr. 34, 843–852.

Zhang N 1992 Electrical impedance tomography based on current density imaging. MS Thesis, University of Toronto, Canada.

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