# A Local Region of Interest Imaging Method for Electrical Impedance Tomography with Internal Electrodes

Authors: Hyeuknam Kwon; Alistair L. McEwan; Tong In Oh; Adnan Farooq; Eung Je Woo; Jin Keun Seo
Journal: Computational and Mathematical Methods in Medicine
 (2013)

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## Abstract

Electrical Impedance Tomography (EIT) is a very attractive functional imaging method despite the low sensitivity and resolution. The use of internal electrodes with the conventional reconstruction algorithms was not enough to enhance image resolution and accuracy in the region of interest (ROI). We propose a local ROI imaging method with internal electrodes developed from careful analysis of the sensitivity matrix that is designed to reduce the sensitivity of the voxels outside the local region and optimize the sensitivity of the voxel inside the local region. We perform numerical simulations and physical measurements to demonstrate the localized EIT imaging method. In preliminary results with multiple objects we show the benefits of using an internal electrode and the improved resolution due to the local ROI image reconstruction method. The sensitivity is further increased by allowing the surface electrodes to be unevenly spaced with a higher density of surface electrodes near the ROI. Also, we analyse how much the image quality is improved using several performance parameters for comparison. While these have not yet been studied in depth, it convincingly shows an improvement in local sensitivity in images obtained with an internal electrode in comparison to a standard reconstruction method.


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## Body

## 1. Introduction

Electrical Impedance Tomography (EIT) is an attractive electrical properties imaging technique for medical applications due to its speed, safety, relatively low cost, and ability to display unique tissue conductivity information. Conventionally, surface electrodes are used to apply currents and record voltages from the boundary of the object of interest such as the thorax, breast, or head. These measurements are used to reconstruct the internal tissue impedances or conductivities using various image reconstruction methods where sensitivity matrix-based approaches are commonly used. Unfortunately, these measurements are insensitive to local impedance changes away from the measuring positions, whereas they are very sensitive to the boundary geometry and impedance changes near the electrodes. To improve the sensitivity and distinguishability in some local internal regions, the use of internal electrodes has been suggested by several researchers [1, 2]. These previous works were concentrated in cardiac applications of EIT as catheters are routinely introduced into various locations during cardiac monitoring, electrophysiology (EP mapping), or cardiac radiofrequency ablation (RFA).EIT with internal electrodes could also be applied to monitoring RFA of liver tumors. RFA is widely used for the treatment of liver tumors such as hepatocellular carcinoma (HCC) and metastatic tumors since many patients are not eligible for surgical resection due to advanced disease, unfavorable location, or impaired clinical condition [3]. Numerous studies have reported that RFA is the most minimally invasive treatment for liver tumors and evaluated it as a successful therapeutic modality, providing reliable outcomes even though its posttreatment recurrence rate is higher than that of cryoablation and resection [4]. Ultrasound and magnetic resonance imaging (MRI) commonly provide the guidance of RFA because they allow real-time visualization of probe placement and high contrast images for tumor and normal tissues [5–8]. Contrast-enhanced computed tomography (CT) and MRI are widely used methods to evaluate ablated lesions by comparing the differences of lesions before and after RF ablation. However, none of these are able to continuously monitor the temperature and changes in properties of cancerous tissue and normal tissue during RFA process.EIT does have this potential due to its high speed, sensitivity to the conductivity change of tumor and normal tissue at various frequencies [9, 10], and its ability to monitor tissue temperature in real time [11, 12]. In both cardiac EIT and EIT for monitoring liver tumour RFA, there are opportunities to add an additional internal electrode close to the region of interest (ROI) to improve EIT sensitivity to internal tissues and particularly to the tissue within the ROI. In both applications, a local imaging reconstruction method with high sensitivity within the ROI is desired since there are significant effects from conductivity changes outside the ROI such as ventilation, perfusion, movement of the lungs, diaphragm, gastric activity, and blood flow in large vessels [13].In this paper, we propose a local sensitivity matrix-based imaging method to increase the sensitivity in a local region of interest near the internal electrode and decrease the sensitivity outside the region of interest to progress the application of EIT to cardiac monitoring and liver RFA. To further increase sensitivity to the ROI, we propose a new arrangement of surface electrodes where the electrode spacing is not equal but more near the ROI. In order to evaluate the performance of the local ROI imaging method, we perform numerical simulations and phantom experiments.


## 2. Method

### 2.1. Conventional EIT Reconstruction Method

Let a bounded domainΩ represent the subject to be imaged. Surface electrodes ℰj for j=1,2,…,E are attached to the boundary ∂Ω, where E is the total number of electrodes. Let γt,ω(r)=σt,ω(r)+iωϵt,ω(r) denote the complex conductivity at time t, angular frequency of ω, and position r. When we inject a sinusoidal current Isin(ωt~) at an angular frequency of ω between a chosen pair of electrodes, a voltage distribution vt,ω(r)sin(ωt~+θt,ω(r)) is formed at the position r. Here, t is used for expressing a slow-time change in the complex conductivity distribution, and t~ is used for the fast-time change to represent time-harmonic fields. The induced time-harmonic potential ut,ω(r)=vt,ω(r)eiθt,ω(r) satisfies the following elliptic partial differential equation [14]:
(1)∇·(γt,ω(r)∇ut,ω(r))=0,forr∈Ω,-γt,ω∇ut,ω·n=g,on∂Ω,
where n is the outward unit normal vector on ∂Ω and g is the corresponding Neumann data on ∂Ω due to the injection current.Static imaging in EIT is difficult due to its fundamental limitations in handling boundary geometry and uncertainty in electrode position. Time-difference EIT (tdEIT) and frequency-difference EIT (fdEIT) use time and frequency difference data, respectively, so that the data subtraction can effectively cancel out common errors related to boundary geometry [14–18]. The difference imaging in EIT is based on linear approximations of the following identities:  (i)
time-difference EIT∇·((∂/∂t)γt,ω(r)∇ut,ω(r))=-∇·(γt,ω(r)∇(∂/∂t)ut,ω(r)),(ii)
frequency-difference EIT∇·((∂/∂ω)γt,ω(r)∇ut,ω(r))=-∇·(γt,ω(r)∇(∂/∂ω)ut,ω(r)).Let the angular frequencyω be fixed. Let ut,ωj denote the time-harmonic potential due to jth injection current between the adjacent pair of electrodes ℰj and ℰj+1. The boundary voltage between ℰk and ℰk+1 due to the jth injection current can be approximated as
(2)Vj,k(t)≈I|ℰ|(∫ℰk‍ut,ωjdS-∫ℰk+1‍ut,ωjdS)≈∫Ω‍γt,ω∇ut,ωj·∇ut,ωkdrforj,k=1,…,E,
where |ℰ| is the surface area of the electrode. The last identity in (2) comes from (1) and divergence theorem. We collect E2 number of boundary voltage data for a sequence of time t=t1,t2,t3,…:
(3)V(t):=(V1,1(t),V1,2(t),…,V1,E(t)︸1stcurrent,V2,1(t),…,V2,E(t)︸2ndcurrent,…,VE,1(t),…,VE,E(t)︸Ethcurrent)T,
where ()T is the transpose. Here, any index number must be understood as a modulus of E.The time-difference data due to the time change ofδγ:=γt2,ω-γt1,ω has the following relation:
(4)Vj,k(t2)-Vj,k(t1)=-∫Ω‍(γt2,ω-γt1,ω)︸δγ∇ut2,ωj·∇ut1,ωjdr.
The linearized method is based on the following rough approximation:
(5)δV:=Vj,k(t2)-Vj,k(t1)≈∫Ω‍δγ∇u*j·∇u*kdr,
where u*j is the potential of  (1) corresponding to a reference conductivity γ=γ*.Discretizing the domain of interest into pixels and assuming thatδγ is constant on each pixel qn, the time-difference EIT problem of (5) can be changed to solve the following linear system:
(6)𝕊δγ=δV.
The nth column of the sensitivity matrix 𝕊 is
(7)sn=(∫qn‍∇u*1·∇u*1dr,…,∫qn‍∇u*j·∇u*kdr,…,∫qn‍∇u*E·∇u*Edr)T.
Hence, the EIT problem is to find a best linear combination of column vectors s1,…,sN which produces δV:
(8)δV≈δγ1s1+⋯+δγNsN.
The column vector sk of 𝕊 represents sensitivity of current-voltage data at the fixed pixel pk, whereas row vectors of 𝕊 represent sensitivity distribution for a fixed current-voltage data. We refer to this approach (combined with a regularization) to reconstruct images as the conventional method throughout this paper.


### 2.2. Local-ROI Imaging Method for EIT

The local-ROI imaging method for EIT is to provide the image of the conductivity change in a local region of interest (ROI) instead of the image in the entire domainΩ. Let a domain D be the local region of interest to be imaged. Imagine that the measured data δV in (5) is divided into two parts
(9)δV=δVD+δVΩ∖D,
where δVD is the voltage change in response to the conductivity perturbation δγ in the local ROI D and δVΩ∖D is the voltage change in response to δγ in Ω∖D. With proper arrangement, we may assume that the first R column vectors of 𝕊 are sensitivity vectors to pixels in ROI D and the other column vectors are sensitivity vectors to pixels in Ω∖D. Then the sensitivity matrix 𝕊 can be decomposed into
(10)𝕊=[𝕊DO]+[O𝕊Ω∖D],
where O represents a proper size of zero matrix,
(11)𝕊D=[∣∣s1⋯sR∣∣],𝕊Ω∖D=[∣∣sR+1⋯sN∣∣].
If we could extract the data δVD by filtering out δVΩ∖D, the global problem (6) can be changed into the local problem:
(12)𝕊DδγD=δVD,
where δγD=[δγ1,δγ2,…,δγR]T. Figure 1(c) shows the reconstructed image of δγD using the localized linear system  (12) via numerical simulation. Comparing this local image with the standard EIT image reconstruction shown in Figure 1(b), it would be desirable to filter out δVΩ∖D to enhance image resolution.Reconstructed images usingδV and δVD via numerical simulations: (a) True image δγ, (b) reconstructed image using δV, and (c) reconstructed image using δVD.
(a)
(b)
(c)For the local imaging in the ROID, we aim to develop a method of extracting VD from the full data V. In order to eliminate the unrelated data VΩ∖D in the linear system (6), we need to find an optimal matrix Φ such that
(13)Φ=argminΦ∥ΦTδV-ΦTδVD∥.
Here, argminΦη(Φ) gives a matrix Φ at which η(Φ) is minimized. If Φ satisfies ∥ΦTδV-ΦTδVD∥≈0, then it eliminates the unrelated data VΩ∖D and we get the localized linear system corresponding to (12):
(14)ΦT𝕊δγ≈ΦTδVD(sinceΦTδV≈ΦTδVD).Note that the quantityλD:=minΦ∥ΦTδV-ΦTδVD∥ depends on the electrode configuration and mesh structure that determines the structure of column vectors of 𝕊 as shown in Figure 2. The λD may not be small when the sensitivity matrix 𝕊 is highly ill-conditioned. If the column vectors s1,…,sR are orthogonal to sR+1,…,sN, then λD=0 by choosing Φ whose rows consist of the column vectors s1,…,sR. But, this is not possible with the standard EIT electrode configuration. We try to find an optimal Φ which minimizes λD. Indeed, cross-correlation μ(j) of column vector in 𝕊 is big if sj is correlated with column vectors in ROI; cross-correlation is defined by
(15)μ(j)=avgpi∈Ω∖D|siTsj|∥si∥2∥sj∥2,forpj∈D.
Figure 3 shows that cross-correlation values decrease by placing internal electrode.Figure 2
Column vectors of the sensitivity matrix are related with pixels inΩ.The cross-correlation distribution onD: (a) μ with internal electrode and (b) μ without internal electrode.
(a)
(b)For finding properΦ, we propose the following minimization
(16)ϕk=argminϕ(∑pj∉D‍|sj·ϕ|2+α∥ϕ-sk∥22),pk∈D,
where α is a suitable parameter. We should note that each ϕk is designed to be close and to be parallel to sk while orthogonal to sj for each pj∉D. The first term in (16), ∑pj∉D‍|sj·ϕ|2, is small when  ϕ is orthogonal to {sj}pj∉D. The second term in (16), ∥ϕ-sk∥22, is small if  ϕ is parallel to sk.  We define a matrix Φ whose columns are consisted of {ϕk}pk∈D:
(17)Φ=(ϕ1,ϕ2,…,ϕR),where⋃n=1Rpn=D.
We multiply ΦT to the linearized system  (6):
(18)ΦT𝕊δγ=ΦTδV.
Now, we have the linear system (18) with the modified sensitivity matrix ΦT𝕊 with the modified data ΦTδV. Here, ΦTδV is regarded as a rough approximation of ΦTδVD.


## 2.1. Conventional EIT Reconstruction Method

Let a bounded domainΩ represent the subject to be imaged. Surface electrodes ℰj for j=1,2,…,E are attached to the boundary ∂Ω, where E is the total number of electrodes. Let γt,ω(r)=σt,ω(r)+iωϵt,ω(r) denote the complex conductivity at time t, angular frequency of ω, and position r. When we inject a sinusoidal current Isin(ωt~) at an angular frequency of ω between a chosen pair of electrodes, a voltage distribution vt,ω(r)sin(ωt~+θt,ω(r)) is formed at the position r. Here, t is used for expressing a slow-time change in the complex conductivity distribution, and t~ is used for the fast-time change to represent time-harmonic fields. The induced time-harmonic potential ut,ω(r)=vt,ω(r)eiθt,ω(r) satisfies the following elliptic partial differential equation [14]:
(1)∇·(γt,ω(r)∇ut,ω(r))=0,forr∈Ω,-γt,ω∇ut,ω·n=g,on∂Ω,
where n is the outward unit normal vector on ∂Ω and g is the corresponding Neumann data on ∂Ω due to the injection current.Static imaging in EIT is difficult due to its fundamental limitations in handling boundary geometry and uncertainty in electrode position. Time-difference EIT (tdEIT) and frequency-difference EIT (fdEIT) use time and frequency difference data, respectively, so that the data subtraction can effectively cancel out common errors related to boundary geometry [14–18]. The difference imaging in EIT is based on linear approximations of the following identities:  (i)
time-difference EIT∇·((∂/∂t)γt,ω(r)∇ut,ω(r))=-∇·(γt,ω(r)∇(∂/∂t)ut,ω(r)),(ii)
frequency-difference EIT∇·((∂/∂ω)γt,ω(r)∇ut,ω(r))=-∇·(γt,ω(r)∇(∂/∂ω)ut,ω(r)).Let the angular frequencyω be fixed. Let ut,ωj denote the time-harmonic potential due to jth injection current between the adjacent pair of electrodes ℰj and ℰj+1. The boundary voltage between ℰk and ℰk+1 due to the jth injection current can be approximated as
(2)Vj,k(t)≈I|ℰ|(∫ℰk‍ut,ωjdS-∫ℰk+1‍ut,ωjdS)≈∫Ω‍γt,ω∇ut,ωj·∇ut,ωkdrforj,k=1,…,E,
where |ℰ| is the surface area of the electrode. The last identity in (2) comes from (1) and divergence theorem. We collect E2 number of boundary voltage data for a sequence of time t=t1,t2,t3,…:
(3)V(t):=(V1,1(t),V1,2(t),…,V1,E(t)︸1stcurrent,V2,1(t),…,V2,E(t)︸2ndcurrent,…,VE,1(t),…,VE,E(t)︸Ethcurrent)T,
where ()T is the transpose. Here, any index number must be understood as a modulus of E.The time-difference data due to the time change ofδγ:=γt2,ω-γt1,ω has the following relation:
(4)Vj,k(t2)-Vj,k(t1)=-∫Ω‍(γt2,ω-γt1,ω)︸δγ∇ut2,ωj·∇ut1,ωjdr.
The linearized method is based on the following rough approximation:
(5)δV:=Vj,k(t2)-Vj,k(t1)≈∫Ω‍δγ∇u*j·∇u*kdr,
where u*j is the potential of  (1) corresponding to a reference conductivity γ=γ*.Discretizing the domain of interest into pixels and assuming thatδγ is constant on each pixel qn, the time-difference EIT problem of (5) can be changed to solve the following linear system:
(6)𝕊δγ=δV.
The nth column of the sensitivity matrix 𝕊 is
(7)sn=(∫qn‍∇u*1·∇u*1dr,…,∫qn‍∇u*j·∇u*kdr,…,∫qn‍∇u*E·∇u*Edr)T.
Hence, the EIT problem is to find a best linear combination of column vectors s1,…,sN which produces δV:
(8)δV≈δγ1s1+⋯+δγNsN.
The column vector sk of 𝕊 represents sensitivity of current-voltage data at the fixed pixel pk, whereas row vectors of 𝕊 represent sensitivity distribution for a fixed current-voltage data. We refer to this approach (combined with a regularization) to reconstruct images as the conventional method throughout this paper.


## 2.2. Local-ROI Imaging Method for EIT

The local-ROI imaging method for EIT is to provide the image of the conductivity change in a local region of interest (ROI) instead of the image in the entire domainΩ. Let a domain D be the local region of interest to be imaged. Imagine that the measured data δV in (5) is divided into two parts
(9)δV=δVD+δVΩ∖D,
where δVD is the voltage change in response to the conductivity perturbation δγ in the local ROI D and δVΩ∖D is the voltage change in response to δγ in Ω∖D. With proper arrangement, we may assume that the first R column vectors of 𝕊 are sensitivity vectors to pixels in ROI D and the other column vectors are sensitivity vectors to pixels in Ω∖D. Then the sensitivity matrix 𝕊 can be decomposed into
(10)𝕊=[𝕊DO]+[O𝕊Ω∖D],
where O represents a proper size of zero matrix,
(11)𝕊D=[∣∣s1⋯sR∣∣],𝕊Ω∖D=[∣∣sR+1⋯sN∣∣].
If we could extract the data δVD by filtering out δVΩ∖D, the global problem (6) can be changed into the local problem:
(12)𝕊DδγD=δVD,
where δγD=[δγ1,δγ2,…,δγR]T. Figure 1(c) shows the reconstructed image of δγD using the localized linear system  (12) via numerical simulation. Comparing this local image with the standard EIT image reconstruction shown in Figure 1(b), it would be desirable to filter out δVΩ∖D to enhance image resolution.Reconstructed images usingδV and δVD via numerical simulations: (a) True image δγ, (b) reconstructed image using δV, and (c) reconstructed image using δVD.
(a)
(b)
(c)For the local imaging in the ROID, we aim to develop a method of extracting VD from the full data V. In order to eliminate the unrelated data VΩ∖D in the linear system (6), we need to find an optimal matrix Φ such that
(13)Φ=argminΦ∥ΦTδV-ΦTδVD∥.
Here, argminΦη(Φ) gives a matrix Φ at which η(Φ) is minimized. If Φ satisfies ∥ΦTδV-ΦTδVD∥≈0, then it eliminates the unrelated data VΩ∖D and we get the localized linear system corresponding to (12):
(14)ΦT𝕊δγ≈ΦTδVD(sinceΦTδV≈ΦTδVD).Note that the quantityλD:=minΦ∥ΦTδV-ΦTδVD∥ depends on the electrode configuration and mesh structure that determines the structure of column vectors of 𝕊 as shown in Figure 2. The λD may not be small when the sensitivity matrix 𝕊 is highly ill-conditioned. If the column vectors s1,…,sR are orthogonal to sR+1,…,sN, then λD=0 by choosing Φ whose rows consist of the column vectors s1,…,sR. But, this is not possible with the standard EIT electrode configuration. We try to find an optimal Φ which minimizes λD. Indeed, cross-correlation μ(j) of column vector in 𝕊 is big if sj is correlated with column vectors in ROI; cross-correlation is defined by
(15)μ(j)=avgpi∈Ω∖D|siTsj|∥si∥2∥sj∥2,forpj∈D.
Figure 3 shows that cross-correlation values decrease by placing internal electrode.Figure 2
Column vectors of the sensitivity matrix are related with pixels inΩ.The cross-correlation distribution onD: (a) μ with internal electrode and (b) μ without internal electrode.
(a)
(b)For finding properΦ, we propose the following minimization
(16)ϕk=argminϕ(∑pj∉D‍|sj·ϕ|2+α∥ϕ-sk∥22),pk∈D,
where α is a suitable parameter. We should note that each ϕk is designed to be close and to be parallel to sk while orthogonal to sj for each pj∉D. The first term in (16), ∑pj∉D‍|sj·ϕ|2, is small when  ϕ is orthogonal to {sj}pj∉D. The second term in (16), ∥ϕ-sk∥22, is small if  ϕ is parallel to sk.  We define a matrix Φ whose columns are consisted of {ϕk}pk∈D:
(17)Φ=(ϕ1,ϕ2,…,ϕR),where⋃n=1Rpn=D.
We multiply ΦT to the linearized system  (6):
(18)ΦT𝕊δγ=ΦTδV.
Now, we have the linear system (18) with the modified sensitivity matrix ΦT𝕊 with the modified data ΦTδV. Here, ΦTδV is regarded as a rough approximation of ΦTδVD.


## 3. Numerical Simulations

In order to analyse the boundary electrode position and the benefit of using an internal electrode with the proposed local-ROI imaging method, we prepared three different kinds of electrode configuration and applied the conventional and local-ROI imaging methods explained in the previous sections. Figure4 shows the cylindrical phantoms with three different electrode configurations. Data obtained from all three electrode configurations were processed by the conventional TSVD reconstruction method. The local-ROI imaging method uses an internal electrode so it was only applied to data obtained with the two internal electrode configurations (Figures 4(b) and 4(c), (Models 1 and 2)). We carry out a total of five numerical simulations, the standard method on Model 0, 1, 2 and the local-ROI method on models 1, 2.(a) Standard EIT phantom without using internal electrode, (b) equidistant surface electrodes with an internal electrode, and (c) unequally spaced surface electrodes with denser spacing near by the ROI with an internal electrode.
(a)
Model 0
(b)
Model 1
(c)
Model 2To compare sensitivity and robustness to noise in the suggested five cases, we simulated an object of 2 S/m conductivity with 0.1428 diameter at (0.8, 0) in the ROI of 1 S/m saline tank. The radius of the ROI is defined by 5/6 of distance between internal electrode and closest boundary electrode. We used two performance indexes to assess the improvement when using an internal electrode and the proposed linear system  (18). First, we computed the singular value threshold to produce the same conductivity contrast of image as shown in Figure 5(a). We repeatedly reconstruct images, updating the singular value threshold, until the same conductivity contrast is produced between the anomaly and background in the reconstructed image. Then we compared the singular value thresholds as a lower number of threshold is an indication of better noise robustness. When we used an internal electrode, the truncated singular value threshold was lower than that without using the internal electrode. Also, the performance of local-ROI imaging method was improved when it was used with unequally spaced surface electrodes with denser spacing near by the ROI. Second, we are concerned about the effect of high contrast anomalies outside the ROI. To investigate this, we examined the sensitivity values of 𝕊 and ΦT𝕊 for each simulation case. The normalized sensitivity values of 𝕊 and ΦT𝕊 from within the ROI and out of ROI are shown separately in Figure 5(b). There was an improved relative sensitivity to the ROI region with the proposed method ΦT𝕊. To show sensitivity values, we calculated the ratio of the matrix norm ∥𝔸in∥/∥𝔸∥ and ∥𝔸out∥/∥𝔸∥ for inside ROI and outside ROI respectively, where 𝔸∈{𝕊 of  Model  0, 1, 2, ΦT𝕊  of  Model  1, 2},𝔸in  is  a  submatrix  of  𝔸  corresponding  to  ROI,𝔸out is  a  submatrix  of 𝔸 corresponding  to  outside  ROI,∥𝔸∥:=sup∥x∥=1∥𝔸x∥.Note that a matrix norm ∥𝔸∥ shows how much 𝔸 deforms x. So, ∥𝔸in∥/∥𝔸∥ and ∥𝔸out∥/∥𝔸∥ show maximum influence of submatrices 𝔸in and 𝔸out for multiplication of 𝔸.Comparison of the conventional and local-ROI imaging method by (a) singular values required to the same conductivity contrast in images and (b) ratio of norms for elements associated within the ROI and outside the ROI for each case.
(a)
(b)In order to compare the performance of the imaging methods in the reconstructed images, we placed multiple objects which had the same conductivity of 0.029 S/m with 0.01 diameter at (0.02, 0.015), (0.02, −0.015), (0.05, −0.015), and (0.05, −0.015) within the ROI of the 0.0418 S/m saline tank as shown in Figure6(a). The conventional reconstructed image without an internal electrode was produced by the TSVD algorithm in Model 0 with diagonal current injection (Figure 6(b)). For comparison of the imaging methods using an internal electrode, we positioned an internal electrode at (0.035, 0) in Model 2. Figures 6(b) and 6(c) show images using the conventional TSVD reconstruction algorithm and the local-ROI imaging method. The proposed method with an internal electrode has better sensitivity and detectability in the ROI.Reconstruction results using simulation data. (a) Simulation configuration for imaging test, (b) conventional TSVD reconstructed image using diagonal injection, (c) TSVD reconstructed image using (6) with an internal electrode, and (d) TSVD reconstructed image using local-ROI imaging method (12) with an internal electrode.
(a)
(b)
(c)
(d)


## 4. Experimental Results

To evaluate the performance of the imaging methods in a physical model, we prepared a cylindrical saline tank with the same geometry, ROI, and electrode positions as Figures4(a) and 4(c) since the denser clustering of boundary electrodes near the ROI (Figure 4(c)) produced better results than the conventional equally spaced electrodes (Figure 4(b)) in the simulation study. The diameter and height of saline tank were 14 cm and 6 cm, respectively. The boundary and internal electrodes were located 3 cm from the bottom in the z direction. The x and y positions of the internal electrode were (3.5, 0) cm relative to the origin (0, 0) at the center of cylindrical tank. The diameter of internal electrode was 0.25 cm and it was covered with insulated rubber except for the end piece of exposed metal. The conductivity of saline was 0.042 S/m. All data was measured by the KHU Mark2.5 EIT system operated at 10 kHz [19].We evaluated the imaging methods using two different situations. First, we located a piece of radish inside of ROI (case 0, 1, 2, 3 (5.6, 0)) and a piece of potato outside of ROI (case 1 (−5.6, 0), case 2 (−3.5, −4), case 3 (0, −5.6)) to assess how the sensitivity of each method is influenced by a high conductivity object in the surrounding area of ROI. The diameter and height of both objects were the same at 1.2 cm and 7 cm as shown in Figure7. The conductivity of radish (0.038 S/m at 10 kHz) was 9.5% lower than saline and the potato (0.029 S/m at 10 kHz) was a higher contrast than the radish with 31% lower conductivity than saline. All data was obtained in the new configuration with an internal electrode and unequal surface electrode spacing as Model 2 in Figure 4(c). All measured data was processed by the conventional TSVD method and the local-ROI imaging method for comparison. We present the norm values of the difference of δV and ΦTδV compared to those values of reference case 0 because it is difficult to analyze images directly from the artifacts due to the large anomaly outside the ROI. Here, we processed reference value by conventional method in case 0 which included only one anomaly (radish) in the ROI. Figure 8(a) shows the effect of the high conductivity contrasted object located outside of ROI. There is less effect with the new local-ROI imaging method when the object outside the ROI is in the opposite hemicircle to the ROI. As the object approaches the ROI (case 1 to case 3) both methods perform similarly.(a) Phantom experimental setup, (b) radish and potato position of case 1, (c) radish and potato position of case 2, and (d) radish and potato position of case 3.
(a)
(b)
(c)
(d)Norm values of difference in experimental data caused by an anomaly outside the ROI in the three different positions given in Figure7.
(a)
(b)Figure8(b) shows the singular value threshold required to produce the same conductivity contrast for each case. The local-ROI imaging method had similar threshold values for all cases with less than 1.73% variation. However the conventional TSVD method showed larger singular values and large dependence on the high contrast anomaly position.Secondly, we evaluated the methods from the reconstructed images in the same configuration as the numerical simulation. We put four carrot objects with 0.04 S/m conductivity at 10 kHz in the 0.06 S/m saline tank. The position of each object was (1.5, 2), (5.5, 2), (5.5, −2), and (1.5, −2) cm, respectively. All objects had the same diameter of 2 cm.We obtained an image in configuration Model 0 during diagonal current injection and TSVD reconstruction. For algorithm comparison, we measured data in Model 2 and applied both methods separately. Figures9(a)–9(c) show the reconstructed images. The proposed local-ROI imaging method with an internal electrode can distinguish inner objects better than conventional methods.Reconstruction results using experimental data. (a) Experiment configuration for imaging test, (b) conventional TSVD reconstructed image using diagonal injection, (c) TSVD reconstructed image using (6) with an internal electrode, and (d) TSVD reconstructed image using local-ROI imaging method (12) with an internal electrode.
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## 5. Conclusions and Discussions

The new local-ROI imaging method has been shown to improve the sensitivity in the ROI region and robustness to noise by comparison of sensitivity matrix values. It provided the approximated linear system with optimized sensitivity matrix to emphasize the detection in ROI. The ROI region is close to an internal electrode and surface electrodes were unequally spaced being more dense close to the ROI. The new method and setup is also less affected by the high conductivity contrasted object outside of ROI. These objects are mimicking a large vessel and several regions of hepatic and metastatic cancers treated by RFA, other gastric organs, or the lungs in cardiac monitoring.Some performance indexes proposed in this paper described that the sensitivity and detectability were obviously improved in simulation and experiment results. However, the reconstructed images did not show improvements as dramatic as we initially expected. One of the major reasons was the ill-posedness of imaging problem. When we designed the optimalΦT matrix that satisfied condition (16), it could not eliminate the effect of unrelated data VΩ∖D completely. Also, the quality of the experimental reconstructed image was highly dependent on the position of an internal electrode and boundary electrodes because we placed the electrodes with denser spacing near by the ROI. Encouragingly with the pilot results of the local-ROI imaging method using an internal electrode, it shows the feasibility and suggests a new approach to improve the resolution of internal local region.An additional improvement which was introduced in this paper was the nonequidistant spacing of electrodes, with the electrodes more densely spaced near the ROI in Model 2 (Figure4(c)). This showed improved results in simulation and so was used in the experimental setup; however, this may be more sensitive to electrode positions, the location of the ROI, or noise. Interestingly in Figure 5(a) we found that this setup of non-equidistant electrodes (Model 2) showed less sensitivity with the conventional EIT method. This may reflect the preference for symmetry with EIT performed in a circular object. The single ROI we investigated was off centre and once we use our local-ROI focusing algorithm there is an improvement found in the non-equidistant electrode setup (model 2).The application of EIT to RF ablation monitoring has high potential; however, we need to study more how to separate the conductivity variations which arise simultaneously from temperature changes and tissue property changes. While the temperature coefficient of conductivity in electrolytes of2% per degree is well known for electrolytes, tissues also exhibit a conductivity dependence on temperature-induced fluid volume shifts which is of the same order of magnitude [20].Lower frequency measurements could be used to discriminate ablated and nonablated tumor and normal tissues. Liver tumour tissue has a higher conductivity than normal liver tissue over 10 Hz to 1 MHz shown by four terminal impedance measurements in excised tissue. Following an ablation, both tissue types showed significantly increased conductivity over the same frequency range indicating that electrical impedance may be used to differentiate tumor tissue diagnostically, for ablation planning and postablation assessment [10].The suggested method may be applied in 3D domain without any additional changes to the algorithm. Here we used a 2D domain analysis because applying the suggested method requires a lot of computations on the column vectors of sensitivity matrix corresponding to pixels in ROI [21]. We need to optimize the local-ROI imaging algorithm by focusing on the ROI and investigate ways to increase the coverage area without moving the electrode position. We may combine the frequency-difference EIT [22, 23] with the local-ROI imaging method to apply frequency-difference data.



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*Source: 964918-2013-07-08.xml*