Accuracy of UWB Path Loss-Based Localization of Wireless Capsule Endoscopy

Wireless capsule endoscopy (WCE) is used to diagnose lesions in the gastrointestinal (GI) tract. The physicians require to know the exact position of the lesions which can be performed by localizing the WCE in the GI tract. In this paper, we propose ultra-wideband (UWB) path loss-based WCE localization and compute the Cramer–Rao lower bound (CRLB) to evaluate the accuracy bounds of localization in the small intestine. First, we propose the estimation of smoothed path loss by minimizing the path loss deviations caused by shadow fading effects of body tissues. Then, the estimated path loss is used to estimate the degree of path loss and to compute the weight of the sensor's positions. Finally, we propose the smoothed path loss degree-based weighted centroid localization (SPLD-WCL) algorithm to estimate the location of the WCE. We simulate the proposed SPLD-WCL algorithm and verify the accuracy by comparing it to the computed CRLB. The proposed SPLD-WCL localization algorithm shows a significantly high accuracy of localization with a 6.83 mm root mean square error (RMSE) without any advanced knowledge of unknown parameters and bounds.


Introduction
Wireless capsule endoscopy diagnoses the abnormalities in the gastrointestinal tract by sending images of the GI tract to an external device by wireless communication. For diagnosis, the physicians require to know the location of the WCE while capturing the image of the abnormalities. Tere are several WCE localization techniques based on magnetic feld strength [1][2][3], radio frequency (RF) [4], or hybrid methods [5,6]. Te received signal strength indicator (RSSI)-based WCE localization techniques are generally based on triangulation or trilateration-based algorithms [4]. Te authors of reference [7] propose triangulation-based 2D positioning of the in vivo RF signal where the signal strength is measured using a wearable antenna array for multiple points of the capsule to estimate the distance. Te reported average error in [8] is 37.7 mm. In [9], the authors exploit spatial sparsity to estimate the position of the emitter using the tissue-adaptive method without estimating the time of arrival (ToA) or path loss. Te authors of reference [9] use the convex optimization theory and l 1 -norm minimization to estimate the position and report less than 7.5 mm RMSE with a perfectly known tissue structure and less than 8.8 mm with an approximately known tissue structure with some levels of uncertainties.
Te localization accuracy of the above traditional RSSIbased methods is infuenced by the hostile RF signal propagation due to the nonhomogeneous tissue properties of the human body. Terefore, new approaches that are robust to channel estimation errors are proposed. In [10,11], the authors propose RSSI-based maximum likelihood (ML) localization using fnite impulse response (FIR) and particle flter-based tracking to fnd the transition model of the capsule. Te authors of reference [11] reported 15 mm RMSE using the FIR flter and 7 mm RMSE using the particle flterbased approach. In [12], the authors use the RSSI-based weighted centroid localization (WCL) approach for capsule localization and reported 24.53 mm RMSE.
International regulatory organizations such as Federal Communications Commission (FCC) [13] recommend medical implant communication service (MICS) band for implant applications which is used in the above-proposed methods of localization [4,[7][8][9][10][11][12]14]. However, highdata-rate communication with impulse radio ultrawideband (IR-UWB) transceivers is also suitable and safe for implantable devices, and it does not interfere much with other radio devices [15]. Short-range, wireless communication using UWB frequency bands is also defned in the IEEE standard 802.15.6 in the vicinity of, or inside, a human body [13]. Te IEEE standard UWB signal propagation models for implantable devices are presented in [13,16,17]. Several UWB-based WCE localization algorithms are available in the literature [18][19][20].
Te authors of reference [18] propose UWB RSS-based capsule endoscopy localization using compressive sensing and the variable noise level (VNL) Kalman flter. Te localization error is 35-60 mm based on the frequency of operation as reported in [18]. In [19], the authors propose UWB 2 × 2 MIMO diversity to estimate the path loss and positionbounded calibrated WCL to localize the capsule in the small intestine. Te reported localization accuracy of the MIMObased approach in [19] is 5.14 mm RMSE using position bounds, whereas it is 7.49 mm without position bounds. However, due to the size and space limitation, higher-order diversity antennas are difcult to be equipped in the capsule, and only 3-dB diversity gain is recommended in [21] for space diversity due to the high correlation among diferent on-body receiver locations. In [20], the authors propose ML estimation for UWB path loss estimation and propose WCL-based localization using position bounds and path loss bounded weight of the sensor receivers. In [20], the reported RMSE error is 6.2 mm for capsule localization in the small intestine using position bounds and 8.14 mm RMSE without using the position bounds. However in [19,20], the authors simulate the proposed capsule localization using the statistical description of UWB propagation through the human chest [16] which is not a suitable scenario for localization in the small intestine. In [19], a calibration coefcient is used which requires prior knowledge of the dimension of the small intestine. Again, for position estimation in both [19,20], position bounds are applied that are computed using the dimension of the small intestine which is practically not feasible. Most of the above-reported works are on developing RSSI-based capsule localization algorithms only. In [22], the authors calculate the accuracy bounds of the RF-based triangulation method for capsule localization using a lognormal channel model of the MICS band. However, no research work is reported in the literature on the accuracy bound of UWB-based WCE localization which can be used as the benchmark to compare the accuracy. Further, in the previous works [4,[7][8][9][10][11][12][18][19][20], the statistical signal propagation using the MICS or UWB frequency band is modeled using the fnite-diference time-domain (FDTD), the fnite integration technique (FIT), or electromagnetic feld simulators, where the signal refections, blood fow, respiration, body movements, antenna alignment, etc. related factors are not considered.
In this paper, we propose a novel method of localization of the WCE using UWB path loss. We also derive and compute the CRLB as the benchmark of the accuracy of the proposed WCE localization in the small intestine. To generate the path loss and to compute the CRLB, we model a small intestine trajectory and map the coordinate values for varying locations of the WCE in the small intestine. Ten, we use the distance between the mapped positions of the WCE and the reference positions of the sensor receivers to generate the UWB path loss using the statistics of the UWB path loss model extracted in [17] considering in-body to on-body in-vivo measurements scenario. Ten, the CRLB is computed using the generated UWB path loss and the proposed scenario of WCE localization. We also propose a novel method of WCE localization using UWB path loss-based weighted centroid localization. Since the UWB path loss is highly deviated by the shadowing efects caused by the nonhomogeneous tissue properties of the human body, we propose the smoothed path loss estimation methods to mitigate the efect of path loss deviations on the accuracy of localization. We estimate the smoothed path loss by fnding the best-ftted path loss of the neighboring location points followed by an averaging method. Te path loss exponents of the best-ftted path loss are estimated by using linear least square regression of the scattered path loss of the neighboring location points. We also estimate the degree of the path loss using the standard deviation of the scattered path loss and the estimated smoothed path loss. Ten, the smoothed path loss is raised to the degree to estimate the weight of the reference sensor receiver's positions. Finally, the position of the WCE is estimated by fnding the weighted centroid of the reference sensor receiver's positions. We evaluate the impact of path loss deviations and the impact of the number of sensor receivers on the accuracy of localization. Te proposed WCE localization algorithm outperforms the other state-of-the-art works in the literature without any prior knowledge of unknown parameters and position bounds. It can localize the capsule with an accuracy of 6.83 mm RMSE which is very close to the computed CRLB.

Localization System Architecture
We propose a WCE localization system, where the WCE is localized using a body-surrounded 3D sensor array of multiple sensor receivers as shown in Figure 1. Te 3D sensor array is placed around the abdominal region of the human body. Here, we consider the transmitter (Tx) to be equipped with the WCE and the sensor receivers (Rx) to be equipped with miniaturized impulse radio (IR) UWB transceivers [15] suitable for the wireless body area network (WBAN).
In our proposed localization approach, the Tx inside the WCE travels through M possible target positions in the small intestine and transmits the UWB signal. Te signal is received by the N sensor receivers of the sensor array. Te RSSI is measured by the N sensor receivers for varying location points of the WCE transmitter in the small intestine. Te scattered path loss is calculated using the transmitted power and the received signal strength. Since the path loss is highly deviated due to the body tissue properties of the human body, the smoothed path loss is estimated using our proposed method. Ten, the degree of path loss is estimated using our proposed method. As the path loss attenuates with the distance, we consider the path loss as a measure of the Tx-Rx separation distance and compute the weight of the sensor receiver's position using the estimated path loss raised to the degree. Finally, the coordinate position of the WCE is estimated using weighted centroid localization by fnding the weighted centroid of the reference positions of the sensor receivers.

Path Loss Model
In our proposed localization approach, the UWB signal between the capsule transmitter and the body-surrounded sensor receivers is scattered due to the diferent material dielectric properties of human body layers along the propagation path. Using the practical scenario, the scattered path loss can be found using the measured RSSI and transmitted power as follows: where, L i is the scattered path loss and P T is the transmitted power. Te scattered UWB path loss is represented as follows: where α, r i , r 0 , and L(r 0 ) denote the ftting constant, separation distance between the capsule transmitter (Tx) and the i th sensor receiver (Rx), reference Tx-Rx distance at 1cm, and the path loss in dB at reference distance r 0 , respectively. Te statistical distribution X(μ, σ 2 L ) of the shadowing term follows a Gaussian distribution model with mean μ and standard deviation of σ L .
Short-range, wireless communication using UWB frequency inside a human body is specifed in the IEEE standard 802.15.6 and characterized by very low power consumption, the smaller size of the antennas, and a higher data rate [13,17]. In [17], the statistics of the UWB signal propagation using a frequency band covering from 3.1 to 6 GHz are extracted using in vivo measurements, where the on-body receiving antennas are located on the abdomen and the in-body positions are located in the small bowel or the colon. Te extracted statistics of the path loss are specifed in Table 1. We generate the scattered UWB path loss using equation (2) by replacing the value of r i and the statistics as available in Table 1. Te Tx-Rx separation distance r i is found for each of the traveling positions of WCE in the small intestine as follows: where, (x r , y r , z r ) are the coordinates of the real position of the capsule transmitter and (x i , y i , z i ) are the coordinates of the reference position of the i th sensor receiver.

CRLB on the Localization Accuracy
In this section, we analyze and compute the accuracy limit of WCE localization in the small intestine by fnding the Cramer-Rao lower bound which provides a benchmark against the accuracy of an unbiased estimator [23]. Terefore, we derive the CRLB as the accuracy bounds of WCE localization by determining the relationship between the path loss estimation error and the location estimation error. Tis is because the accuracy of WCE localization is mostly infuenced by the path loss estimation error. Te path loss estimation error occurs due to the scattering of the path loss caused by the nonhomogeneous tissue properties of the human body. Te scattered path loss is represented as equation (2), where X(μ, σ 2 L ) is the scattered shadowing term with mean μ and standard deviation of σ L . Tus, the best-ftted mean path loss excluding the scattering term can be expressed as follows: and the standard deviation of path loss, σ L , can be given as follows: where N is the total number of sensor receivers. In the following subsections, we estimate the CRLB on the variance of path loss to relate it to the CRLB of the localization error.  mean L(r i ) and standard deviation σ L as shown in the following:

CRLB on the
Te Cramer-Rao lower bound (CRLB) on the variance of the path loss estimator must satisfy the following equation: Diferentiating the logarithm of equation (6) once with respect to best-ftted mean path loss (L), we get the following equation: Te expected path loss L(r i ) can be achieved by equating equation (8) to zero. Diferentiating equation (8) results in the following equation: Tus, CRLB on the variance of path loss is obtained as follows: 4.2. CRLB on the Variance of Localization. Te PDF of path loss for an unknown location of the capsule can be expressed as follows: where r i is the distance between Tx-Rx, and it is a function of the 3D coordinate (x, y, z) positions of the capsule. Te CRLB on the variance of the location estimator must satisfy the following equation: Diferentiating the logarithm of equation (11) once with respect to x-y-z coordinate positions, we get the following equation: Diferentiating (13), we get thefollowing equation: Tus, the CRLB on the variance of localization is obtained as follows: To compute the CRLB, we diferentiate the expected mean path loss L(r i ) in equation (4) with respect to x-y-z coordinates and get the following equation: Te equation (16) can be written in matrix form as follows: and we can write, dL dr where, dL � dL r 1 dL r 2 ⋮ dL r N ; Finally, replacing equations (18) and (15), the CRLB on the variance of localization is obtained as follows: Tus, we can compute the CRLB on the localization error as follows: For M possible positions of the capsule, the CRLB on the root mean square error (RMSE) of localization can be computed as follows:

Proposed WCE Localization Algorithm
We propose a WCL-based localization algorithm to localize the three dimensional position of the WCE in the small intestine. WCL estimates the position of the implanted capsule by fnding the weighted average of the sensor receivers' position as follows: where, P(x e , y e , z e ) is the estimated x-y-z coordinate position of the capsule, N is the number of sensor receivers, S i (x i , y i , z i ) is the reference x-y-z coordinate position of the i th sensor receiver, and W i is the weight of the reference position of the i th sensor receiver which is inversely proportional to the distance of the sensor receivers from the capsule transmitter. Te detail methodologies of the proposed algorithm are shown in Algorithm 1 and explained in the following: Journal of Healthcare Engineering

Path Loss Estimation.
Path loss is estimated as a measure of Tx-Rx distance and to compute the weight of the reference positions of the sensor receivers. Te propagation path loss is scattered due to the shadowing efect caused by the nonhomogeneous human tissue dielectric properties. To get an accurate estimate of the path loss, the scattering of the path loss is required to be minimized. Te capsule travels M possible points through the small intestine. Te best-ftted path loss of the adjacent traveling location points can be estimated as follows: where k � (j − n L ): (j + n R ) is the range of n R + n L + 1 adjacent location points of the capsule at j th instant, n L is the lower bound, n R is the upper bound of the adjacent location points, and c 1 and c 2 are the path loss exponents. Te path loss exponents are estimated by using linear least square regression of the scattered path loss measured at the adjacent location points of the capsule as follows: where C is a matrix of the path loss exponents, L is the matrix of the measured path loss of n R + n L + 1 adjacent location points of the capsule, and K is the set of n R + n L + 1 adjacent location points.
Using the extracted path loss exponents c 1 and c 2 , we can estimate the smoothed path loss, PL ij , between the i th sensor receiver and j th location point by averaging the best-ftted mean path loss of the adjacent location points as follows:

Weight Calculation.
Te weight of the reference position of the sensor receivers is inversely proportional to Tx-Rx distance. As the path loss is a measure of Tx-Rx distance, we can compute the weight using the estimated smoothed path loss and the estimated degree of path loss as follows: where c is the degree of path loss. c is dependent on the propagation path loss caused by the shadowing environment. Tus, we can estimate the degree c by fnding the standard deviation of path loss (σ L ) as follows: � α(r ij /r 0 ) + L(r 0 ) + X(0, σ 2 L ) {Generated scattered path loss} 5 end for 6 end for 7 for j � 1, 2, . . . , M do 8 k � (j − n L ): 1: (j + n R ) 9 for i � 1, 2, . . . , N do 10 L � L ik {Scattered path loss of k adjacent positions} 11 C � (K T K) − 1 K T L {Extraction of path loss exponents} 12 end for 13 PL ij � 1/(n R + n L + 1)  Journal of Healthcare Engineering where M is the number of location points, N is number of sensor receivers, and L ij and PL ij are the measured scattered path loss and the estimated smoothed path loss between the i th sensor receiver and the j th location position of the capsule, respectively.

Position Estimation.
Finally, we estimate the 3D position of the capsule using WCL. We put the calculated weight of the sensor receiver's position in equation (23) and estimate the j th instant position of the capsule as follows:

Performance Metrics
We apply the following three performance metrics to evaluate the accuracy of the proposed path loss estimation and position estimation methods.

Coefcient of Determination, R 2 .
Te coefcient of determination (R 2 ) measures how well a statistical model predicts an outcome. Te outcome is represented by the model's dependent variable. Te lowest possible value of R 2 is 0, and the highest possible value is 1. Te better a model is at making predictions, the closer its R 2 will be to 1. Te formula of the coefcient of determination (R 2 ) is as follows: where RSS is the sum of squared residuals and TSS is the total sum of squares. We use R 2 to verify the performance of the proposed path loss estimation and position estimation methods. For the path loss estimation method, we calculate the coefcient of determination of path loss, R 2 pl , as follows: (33)

Localization Error (LE).
Te localization error is a performance metric that is simply measured by the difference between estimated and real positions as follows: where (x r , y r , z r ) are the coordinates of the real positions and (x e , y e , z e ) are the coordinates of the estimated positions. Te LE is compared to the computed CRLB of the LE as a benchmark to verify the accuracy of localization.

Root Mean Square Error (RMSE).
Te RMSE is a performance metric which is computed as follows: where M is the total number of possible positions traveled by the capsule, (x r j , y r j , z r j ) are the coordinates of the j th real position of the capsule, and (x e j , y e j , z e j ) are the coordinates of the j th estimated position of the capsule. Te RMSE is compared to the computed CRLB of the RMSE as a benchmark to verify the accuracy of localization.

Simulation and Results
We simulate the proposed localization algorithm using a 3D simulation platform developed in MATLAB as shown in  Table 2.
To evaluate the performance of the proposed localization algorithm, we use three performance metrics, R 2 pos , the LE and the RMSE, as shown in equations (33), (34), and (35), respectively. To compare the performance to a benchmark accuracy, we compute the CRLB on the variance of localization as shown in equation (20). It is apparent from equation (20) that the performance is dependent on the standard deviation of path loss σ L and the Tx-Rx separation distance. As we know that for our proposed localization approach, the path loss is highly deviated due to the material properties of the human body layers. Terefore, to generate the scattered path loss between the Tx-Rx, we use the statistical path loss parameters as specifed in Table 1 that are extracted in [17] for ingestible devices using the in-body to on-body in vivo measurement scenario. Ten, we generate the scattered path loss and best-ftted mean path loss using Journal of Healthcare Engineering equations (2) and (4), respectively, by replacing the value of Tx-Rx separation distance r i and the path loss statistics as available in Table 1. Te distance r i between the reference coordinate positions of the sensor receivers and all the mapped 2443 traveling positions of the capsule are calculated using equation (3). Figure 3 illustrates how the path loss varies with the Tx-Rx separation distance and how the path loss is scattered around the best-ftted path loss due to the standard deviation of path loss σ L . Te path loss deviation σ L and the channel response H are calculated using equations (5) and (19) for diferent number of sensor receivers and replaced in equation (20) to compute the CRLB on the variance of localization. Finally, the CRLB on the LE and the RMSE are computed using equation (21) and (22), respectively. Figure 4 shows the CRLB on the LE for all positions as a function of the standard deviation of path loss, σ L . It is observed in Figure 4 that the CRLB on the LE increases with path loss deviation σ L .
To minimize the deviation in the scattered path loss, we estimate the smoothed path loss using our proposed method using equation (27). Te path loss exponents c 1 and c 2 are estimated using LLS regression as shown in equation (26). Te lower and upper bound of the adjacent location points were set to 11 to obtain optimal results. Te performance of our proposed path loss estimation method is evaluated using the performance metric R 2 pl as shown in equation (32). Te R 2 pl value using 8 sensor receivers is 0.9971 and using 48 sensor receivers is 0.9974, indicating a very high coefcient of determination at making predictions.
Next, we simulate the proposed smoothed path loss degree-based WCL (SPLD-WCL) algorithm using 8-48 sensor receivers to estimate the position of the capsule traveling through the small intestine. Figure 2 shows the simulation results with 48 sensor receivers and illustrates the real and estimated positions of 2443 simulated positions of the capsule in the small intestine trajectory. Te performance is evaluated using the R 2 pos , the LE, and the RMSE. Table 3 -100 Rx (-100 ,      summarizes the results obtained using diferent improvement steps of the algorithm. It is observed from the results in Table 3 that the R 2 pos improves and the RMSE reduces signifcantly by applying diferent improvement steps of the proposed algorithm. Figure 5 illustrates the localization error of all simulated positions by applying diferent improvement steps of the proposed algorithm. It is apparent from Table 3 and Figure 5 that a major improvement is obtained by applying the improvement steps, especially by applying path loss smoothing and by raising the path loss to the estimated degree c. It is also observed that the accuracy is improved by raising the degree of both the scattered path loss and the smoothed path loss. Figure 5 and Table 3 also compare the accuracy to the computed CRLB. It is observed that the localization error and the RMSE of the proposed methods are very close to the computed CRLB. We analyze the impact of the sensor receivers on the accuracy of the localization by varying the number of sensor receivers from 8 to 48. In our proposed approach of localization using WCL, the WCE is localized by fnding the weighted centroid of the sensor receivers' positions. Terefore, at least 8 sensor receivers are required to be placed at the 8 corner points of the 3D cubical array to localize the capsule traveling through the central locations of the cube by fnding the weighted centroid. It is observed in Table 3 that using four (04) sensor receivers, we obtain a negative R 2 pos value. Tus, a minimum of 8 receivers are required for 3D localization of the WCE using WCL. Te cumulative distribution of the localization error (LE) for an increasing number of sensor receivers is demonstrated in Figure 6. It is observed that for 2443 simulated positions, 80% of localization error remains below 12 mm by using 8 sensor receivers, whereas by using 48 sensor receivers, 80% of the localization errors remain below 10 mm. Figure 7 illustrates the RMSE accuracy of the proposed SPLD-WCL for an increasing number of sensor receivers and compares it to the computed CRLB. It is observed in Figure 7 that the RMSE of the proposed SPLD-WCL algorithm and the CRLB decrease with the increasing number of sensor receivers. Te computed CRLB on the RMSE is 3.96 mm and 0.664 mm using 8 and 48 sensor receivers, respectively. For 2443 simulated positions of the capsule, the RMSE of localization using the proposed SPLD-WCL localization algorithm is 8.7 mm and 6.83 mm using 8 and 48 sensor receivers, respectively. Table 4 compares the methods and the obtained localization accuracy of the proposed SPLD-WCL algorithm to other works in the literature. As we can see from the comparison in Table 4, the proposed localization algorithm shows signifcantly high localization accuracy using 8 to 48 sensor receivers using the in-vivo UWB channel model as compared to the state-of-the-art methods of other works in     the literature by applying the proposed methods of smoothed path loss estimation, path loss-based degree estimation, and the WCL. Tus, it may be concluded that the proposed SPLD-WCL localization algorithm outperforms the literature without any prior knowledge of unknown parameters, distance, or channel statistics with a signifcantly high accuracy close to the benchmark CRLB.

Conclusion
In this paper, we have proposed WCE localization in the small intestine using the SPLD-WCL algorithm using the UWB signal propagation between the capsule transmitter and sensor receivers of the body-surrounded sensor array. We have also found the CRLB as the benchmark of localization accuracy using the UWB signal propagation model. Te performance of the proposed algorithm has been evaluated using the performance metrics, R 2 , the LE, and the RMSE. For the simulation, we have modeled a small intestine trajectory mapped with 2443 target positions of the WCE in 1 mm resolution. Ten, we have generated the path loss using the UWB path loss statistics and the coordinate positions of the WCE in the small intestine trajectory model and the sensor receivers in the proposed localization scenario. Next, we have computed the CRLB on the LE and the RMSE using the generated path loss for the proposed localization scenario. Te computed CRLB on the RMSE is 3.96 mm and 0.664 mm using 8 and 48 sensor receivers, respectively. To develop the proposed localization algorithm, we have proposed smoothed path loss estimation to minimize the efect of the path loss deviation on the localization accuracy. We have also proposed a method of determining the degree of the path loss using the standard deviation of the scattered path loss and the smoothed path loss which does not require knowledge of any unknown parameters. Ten, we have computed the weight of the sensor receivers using the estimated path loss raised to the degree and found the position of WCE using weighted centroid localization. We have simulated the proposed localization algorithm to localize the WCE at 2443 target positions in the small intestine. Te proposed methods show signifcantly high accuracy in path loss estimation and localization of the WCE in the small intestine. Te accuracy of the path loss estimation methods in terms of R 2 pl is 0.9971 and 0.9974 using 8 and 48 sensor receivers, respectively, indicating a very high level of signifcance in making predictions. We have also analyzed the impact of the number of sensor receivers and the path loss variance on localization accuracy. We have seen that the accuracy of localization improves by increasing the number of sensor receivers. It is also found that the accuracy of localization improves signifcantly by applying path loss smoothing and the degree of path loss. Te measured coefcient of determination of the positions, R 2 pos , is 0.9901 which indicates a signifcantly high level of estimation. Te simulation results show that the RMSE of the proposed localization algorithm is 8.7 mm and 6.83 mm using 8 and 48 sensor receivers, respectively, which is very close to the benchmark CRLB. Tus, it may be concluded that the proposed SPLD-WCL localization algorithm can obtain signifcantly high accuracy as compared to the state-ofthe-art works in the literature without any prior knowledge of distances, bounds, and any unknown parameters.

Data Availability
Te dataset used to support the fndings of this study is available from the corresponding author upon request.

Conflicts of Interest
Te authors declare that there are no conficts of interest.