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Characterization of path loss and absorption for a wireless radio frequency link between an in-body endoscopy capsule and a receiver outside the body


Physical-layer characterization is important for design of in-to-out body communication for wireless body area networks (WBANs). This paper numerically investigates the path loss and absorption of an in-to-out body radio frequency (RF) wireless link between an endoscopy capsule and a receiver outside the body using a 3D electromagnetic solver. A spiral antenna in the endoscopy capsule is tuned to operate in the Medical Implant Communication Service (MICS) band at 402 MHz, accounting for the properties of the human body. The influence of misalignment, rotation of the capsule, and three different human models are investigated. Semi-empirical path loss models for various homogeneous tissues and 3D realistic human body models are provided for manufacturers to evaluate the performance of in-body to out-body WBAN systems. The specific absorption rate (SAR) in homogeneous and heterogeneous body models is characterized and compliance is investigated.


A wireless body area network (WBAN) connects nodes that are situated on or in the body of a person. Applications of WBANs include medicine and health care, sports, and multimedia. As it facilitates movement among users, it has brought about a revolutionary change in patient monitoring and healthcare facilities. Active implants placed within the human body lead to better and faster diagnosis, thus, improving the quality of life of the patient. The development of an endoscopy capsule system enables the examination of areas of the small intestine that cannot be seen by other types of endoscopy. The benefits of the capsule endoscopy in terms of a better diagnosis are obvious. Also, the patient’s comfort improves, as there are no wires or tubes involved in the procedure.

The characterization of the physical layer of the network is an important step in the development of a WBAN. A lot of studies investigated on-body propagation [111]. Less literature is available on modeling of propagation loss within or in-to-out the human body [1217] and often the focus is on 2.4 GHz. A path loss (PL) model for in-body wireless implants (biocompatible implantable antennas) is proposed in [12]. Scenarios for channel modeling for an endoscopy application are proposed in [14]. In [13] and [18] similar investigations were presented, but both of them proposed the 2.4 GHz frequency band, which led to a smaller antenna. In addition, in-body to in-body communication is examined. The influence of different tissues at various frequencies is characterized for an in-to-out channel in [19], but the antenna design was not specified. A multi-implant scenario at 2.4 GHz is investigated in [20] using insulated dipole antennas for specific locations such as the liver, heart, spleen, and the kidneys. A spiral antenna at 450 MHz for ingestible capsule endoscope systems is designed in [21].

The objective of this paper is to investigate numerically the PL of an in-to-out body radio frequency (RF) wireless link between an endoscopy capsule and a half-wavelength dipole (reference receiver) outside the body using a 3D electromagnetic solver, applying the finite difference time domain (FDTD) method. This study focusses on the 402 to 405 MHz Medical Implant Communication Service (MICS) band. The spiral antenna for an endoscopy capsule operating at 450 MHz proposed by [21] is selected as the transmitter and tuned to operate at 402 MHz by changing its dimensions. This spiral antenna fits inside a capsule and is experimentally validated in a human phantom and a pig under general anesthesia. Therefore, we selected this antenna for our propagation analysis. Both antennas are dimensioned with the FDTD simulation platform SEMCAD-X. Path loss for the in-to-out channel and the specific absorption rate (SAR) are investigated for homogeneous and heterogeneous tissues of three human models, namely, an adult, an obese adult, and a child. The influence of the dielectric properties of the tissue on the PL is evaluated and compliance of the electromagnetic absorption with the international guidelines of the International Commission on Non-Ionizing Radiation Protection (ICNIRP) [22] is evaluated for the maximum allowed radiated power.

The analysis of this research can be used by manufacturers to evaluate the performance of in-body to out-body WBAN systems and to carry out link budget calculations, since it is difficult for them to test their systems on actual humans. This research also enables to better estimate the energy consumption of the endoscopy capsule and thus, the battery lifetime, which is limited due to the small size of the pills. Another application of the models of this paper is cross-layer design, where the proposed models are used to evaluate communication protocols for WBANs and the energy consumption in short-range wireless networks [6].

Frequency selection

The wireless connection between the devices of a WBAN can occur at different frequencies. Most published models use the industrial, scientific, and medical (ISM) frequency bands or UWB (ultra-wideband). Among these, the most commonly used frequencies in medical communications are 402 MHz, 868 MHz, and 2.4 GHz. The choice of the optimum frequency is an important factor taking into account attenuation, tissue conductivity, and also antenna size and orientation, which can affect not only radiation inside the body but can also determine the optimum distance of which good performance can be achieved in the surrounding environment. The MICS band is a licensed band used for implant communication and has the same frequency range (402 to 405 MHz) in most countries [23].

The MICS band does not support high data rate applications. The ISM 2.4 GHz band supports higher data rate applications and is available worldwide. However, there are high chances of interference as many wireless devices operate at ISM band and a higher attenuation in the body occurs due to the higher frequency. This results in a need to increase the transmitting power, which is a disadvantage in cases where the antenna is embedded within the human body, leading to higher power consumption and possible non-compliance with international exposure guidelines [22]. Thus, MICS is a lower power frequency band, with less risk to encounter interferences. It allows longer communication links because the attenuation is lower. A disadvantage is that the size of the antennas increases. According to the authors’ knowledge, there is only a small amount of studies about in-to-out body propagation for this band.



Homogeneous tissues

The path loss is investigated for three different tissues using the 3D FDTD solver SEMCAD-X at 402 MHz: muscle tissue (permittivity ε r =57.1, conductivity σ=0.8 S/m), skin tissue (ε r =46.7, σ=0.69 S/m), and esophagus tissue (ε r =67.5, σ=1 S/m) are considered. These represent relevant tissues for the endoscopy configuration [14]. The simulation settings are the same in all the cases. Harmonic simulations at 402 MHz are run with a simulation time of 14 periods. UPML (uniaxial perfectly matched layer) boundaries terminate the simulation domain and absorb 95% of the incident power. The padding is set to λ/4. A maximum grid step of 2 mm is applied inside the body. Aligned and misaligned configurations and rotation of the transmitting spiral antenna in the capsule are investigated. Figure 1 shows the investigated configuration.

Figure 1
figure 1

Configuration for the path loss analysis between capsule in the homogeneous tissue and receiver outside. d = antenna separation, d v = vertical displacement.

Heterogeneous phantom models

Three heterogeneous models are investigated: a 6-year-old boy (denoted Thelonius), an adult man (denoted Duke), and an obese adult man (denoted Fats) [24]. The Virtual Population models are based on magnetic resonance images (MRI) of healthy volunteers. The tissue properties for the frequency of 402 MHz are assigned from Gabriel’s database [25] and a maximum grid step in the body of 2 mm is used.

The PL and the SAR at 402 MHz are investigated in these models and compared with those in homogeneous tissues. The digestive tract is investigated, so the endoscopy capsule is placed at positions inside the tract as shown in Figure 2. The free-space dipole is positioned outside the body and the PL between the two antennas is evaluated for two configurations: the free-space dipole is situated in a fixed position at a distance of 18.5 cm from the body next to the arm in the case of the adult man and the obese man (Figure 2a) and at 13.5 cm in front of the body for the child model, at the height of the large intestine (Figure 2b), since most of the points of the digestive tract are located there.

Figure 2
figure 2

Configuration: locations of endoscopy capsule along digestive tract in realistic human body models. (a) Adult man Duke. (b) 6-Year-old boy Thelonius. Squares indicate investigated positions of the capsule.

Positions along the tract through the pharynx, the esophagus, the stomach lumen, and the small and large intestines lumen are selected with separations of 20 mm in the z-direction, while the x- and y-separation is 22 mm in the large intestine and 20 mm in the stomach and the small intestine. The spiral antenna is placed in every selected position as indicated in Figure 2a,b ((a) for adult and (b) for child). Figure 3 shows Fats and the locations of the endoscopy capsule. The files are run using very high (99.9%) absorbing boundaries and a padding of λ/4.

Figure 3
figure 3

Fats, a 37-year-old obese model (120 kg) of the Virtual Population and locations of endoscopy capsule.

Antenna dimensioning

In this paper, it is not the goal to design suitable in-body antennas but to characterize the propagation from in-to-out the body. As a receiving antenna outside the body, a half-wavelength dipole is selected. The free-space dipole is modeled and tuned to resonate at 402 MHz. The thickness of the perfect electric conductor (PEC) structures is set at 2 mm and the gap is 1 mm. With respect to the transmitting antenna selection inside the body, PIFA (planar inverted-F antenna), dual-band microstrip patch antennas, and spiral antennas are often used for medical applications. In general, PIFA antennas are employed in artificial cardiac pacemakers and difficult to fit inside a pill. The size of the antenna is a factor of importance at 402 MHz. The spiral antenna [21] is the smallest among the different options and therefore it is selected for the investigation.

Spiral antenna in capsule

A small spiral antenna designed for an endoscopy capsule by [21] is selected and tuned to 402 MHz. The antenna is composed of a spiral PEC structure and a ground plane separated at a certain distance to place the source in between (see Figure four of [21]). The shell of the capsule consists of a dielectric (Ultem material, ε r =3.15,σ=0 S/m). Figure 4 shows the capsule, antenna, and its dimensions.

Figure 4
figure 4

Capsule with spiral antenna and dielectric containers tuned to 402 MHz[21].

The length L is an important parameter in the design of the spiral because it determines the resonance frequency. In addition, the spiral has to fit in the capsule. In this case, an antenna with 4.98-mm radius is modeled.

The thickness of the shell is 0.25 mm. The ground plane has a radius of 5 mm and a height of 0.5 mm. The capsule is closed at the bottom by a circular Ultem sheet with a thickness of 0.5 mm.

The influence of the (i) height and (ii) the length of the spiral, (iii) the effect of the gap between the antenna and the ground plane on the radiation characteristics (resonance frequency fres and S11 with respect to 50 Ω) are investigated, as well as (iv) the robustness of the spiral when immersed in different tissues. Frequency settings for performing broadband simulations in the FDTD simulation platform are as follows: a central frequency of 402 MHz and a bandwidth of 0.4 GHz. In this way, the influence of the geometric parameters (mentioned above) is characterized. Based on the above parametric studies, dimensions for optimal antenna characteristics for the spiral antenna of the endoscopy capsule are selected. The parameters for the spiral antenna configuration used in this paper are listed in Table 1. Note that the antenna is not a very good radiator. The S11 value is about −5.5 dB due its small dimensions, which means that about 30% of the power is reflected at the input terminals. Because this paper is focussed on the path loss and propagation effects, this is not a problem for our analysis. We prefer to use here an actual usable antenna instead of e.g., a larger antenna at 402 MHz [20], which does not fit in the digestive tract of a human. Figure 5 shows the reflection coefficient |S11|dB of the resulting spiral antenna in the three considered tissues with the dimensions of Table 1. A gap g of 4 mm is selected here (Figure 4, Table 1). The extension of the gap is limited by the size of the capsule. The reflection characteristics vary depending on the tissue: the −5 dB bandwidth in Figure 5 for the different tissues is more than 45 MHz, which is sufficient for the MICS band. |S11| at resonance is −7 dB in muscle and −5.5 dB in esophagus tissue. The lower |S11| value for muscle is due to the lower permittivity (57.1 versus 67.5 in esophagus), which results in a better ‘matching’. By changing the length of the spiral, the resonance frequency can be tuned. Longer PEC (perfect electric conductor) structures lead to lower resonance frequencies. In tissues with lower permittivity, the PEC structure has to be larger to resonate at 402 MHz comparing to the esophagus tissue. Increasing the length of the spiral makes the resonance frequency to be closer to 402 MHz, here we selected a length of 81 mm. Keeping the overall dimensions of the pill and tuning of the antenna - tuning for lower frequencies increases the antenna size - results in a reduced antenna efficiency or performance. If we compare the return loss of our antenna tuned at 402 MHz and the antenna of Lee et al. [21] at 500 MHz in a tissue with the same conductivity of 1 S/m, then we obtain a return loss of −7 dB, which is satisfactory for communication (see Figure 5).

Table 1 Spiral antenna characteristics
Figure 5
figure 5

| S 11 | (dB) of spiral antenna in capsule for three different tissues.

Path loss in homogeneous tissues

This section discusses the in-to-out body propagation and path loss for homogeneous tissues. PL models are presented and the influence of misalignment, rotation in the body, and the absorption are determined. We analyze here first homogeneous tissues because the influence of different parameters (dielectric tissue properties, tissue separation, alignment, etc.) can be investigated separately. This allows manufacturers to select a tissue with the highest absorption and thus highest path losses. Moreover, in this paper we aim at comparing the propagation in homogeneous tissues with the heterogeneous models. In contrary to layered tissues, homogeneous tissues can be replaced by liquids in practical setups to evaluate the performance of endoscopy capsules and systems of manufacturers.

Analysis of in-to-out body propagation

PL is defined as the ratio of the input power at port 1 (Pin) to the power received at port 2 (Prec) in a two-port setup. PL in terms of transmission coefficient is defined as 1/|S21|2 with respect to 50 Ω.

PL | dB =( P in / P rec )=10 log 10 | S 21 | 2 =| S 21 | dB .

This allows us to regard the setup as a two-port circuit for which we determine |S21|dB with reference impedances of 50 Ω at both ports. To model the path loss between the transmitting and the receiving antenna as a function of the distance, we use the following semi-empirical formula, expressed in dB and based on the Friis formula [26]:

PL dB (d)= PL 0 , dB +10nlog(d/ d 0 )=| S 21 | dB ,

where the total antenna separation d is expressed in millimeter in this paper, PL0,dB is the path loss in decibel at a reference distance d0 (250 mm in this paper), and n [-] is the path loss exponent, which equals to 2 in the free space.

The antenna is included as a part of the channel model throughout this analysis [6, 13, 18, 20, 27].

Influence of antenna separation for different tissues

Figure 6 shows the PL as a function of the distance between the spiral and the dipole outside the body when the antennas are aligned. PL increases of course when the separation increases. In Figure 6a the spiral is moving horizontally in the tissue and the dipole is fixed at 10.5 mm from the medium (Figure 1). In Figure 6a the dipole outside the tissue is moving (starting from the position in Figure 1) and the spiral is fixed in the tissue at 150 mm from the tissue-air interface (Figure 1). The highest PL in Figure 6 is obtained for the esophagus tissue with the highest conductivity of the considered tissues (ε r =67.5, σ=1 S/m), followed by muscle tissue (ε r =57.1, σ=0.8 S/m), and skin tissue (ε r =46.7, σ=0.69 S/m). PL is more affected by the variation of the conductivity of the different tissues, resulting for the highest PL values for esophagus in Figure 6. PL increases with increasing conductivity of the tissue and decreases with increasing permittivity [18]. In this range of tissue permittivities, the variation on the PL is about 2 dB, while for the range of conductivities, the variation is almost 8 dB [18]. The flattening of the curves in Figure 6a for distances longer than 180 mm is due to the finite size of the homogeneous tissue simulations; the electromagnetic waves are partly reflected at the upper and lower tissue boundaries.

Figure 6
figure 6

Path loss versus separation distance between antennas. (a) When moving the spiral horizontally (dipole fixed at 10.5 mm from the tissue, Figure 1). (b) When moving the dipole horizontally (spiral is fixed in the tissue at 150 mm from the tissue-air interface).

Figure 6b shows the PL when moving the dipole away from the spiral. When the distance between the antennas is 160.5 mm, the dipole is only 10.5 mm from the tissue surface (Figure 1). At this distance, the coupling between dipole and tissue-air interface decreases the PL. For further separations the PL increases again.

Table 2 summarizes the parameters of the PL models for homogeneous tissues in this paper, obtained using Equation 2 and fitting the parameters PL0,dB and n to the simulation data. The path loss exponents in the tissues are similar and about equal to 3. The homogeneous esophagus tissue has a higher path loss constant PL0,dB (61 dB compared to 56 to 57 dB) due to the higher conductivity compared to the muscle and skin tissues. The R2 values (coefficient of determination) are about 0.99, indicating the linear relationship between PL (in decibel) and distance, as these models are deterministic.

Table 2 Parameters for path loss models for homogeneous and heterogeneous tissues and phantoms ( d 0 =250 mm)

Influence of antenna misalignment

To study the influence of the misalignment, the antennas are shifted vertically. First, an antenna separation of 160.5 mm (spiral is positioned 150 mm from the tissue boundary, see Figure 1) is selected and the spiral is shifted vertically with a vertical displacement d v from −100 mm to +100 mm. Figure 7 shows the PL for vertical displacement dv of the spiral. The curves are almost symmetric and the small disagreement is due to the spiral’s non-symmetric form. The PL increases by 3.3 dB, considering the same tissue when the spiral is shifted at 100 mm. The highest PL occurs in the esophagus tissue due to the highest conductivity. For larger separations d (250 to 360 mm), misalignment between antennas causes the in-to-out body link to experience 10 to 12 dB differences for the same distance. Table 2 shows the influence of misalignment on the PL models: misalignment between antennas increases the path loss exponent to more than the double of when the antennas are aligned (n=3 to n=6.9 when misaligned in esophagus). Moreover the PL constant P L0,d B increases about 7 dB when misaligned (69 dB compared to 61 dB for esophagus in Table 2).

Figure 7
figure 7

Path loss versus vertical displacement d v of the spiral.

Influence of antenna rotation

The evaluation is performed for the esophagus tissue because the losses are the highest. Since the spiral is nearly symmetric, the influence of rotation around the z-axis is negligible. Only rotation around x-axis and y-axis is investigated. Figure 8a,b shows the PL when the spiral is rotated around the x- and y-axis, respectively. The figure is symmetrical because the position of the spiral with respect to the dipole is the same when it is rotated for positive and negative angles. When the rotation angle is 90° or −90°, the PL is maximum, because the transmitter is completely perpendicular to the dipole and is not pointing to it (Figure 1). The minimum PL around x-axis is obtained with a rotation angle of 30°. The variation on the PL (Δ PL) for rotation around the x-axis is 4 dB. Analog results are obtained when rotating around the y-axis. The variation Δ PL for rotation around the y-axis is 10 dB.

Figure 8
figure 8

PL versus spiral rotation angle around x - and y -axis.

The effect of the rotation around this axis is larger because the spiral changes from pointing to the dipole to pointing directly to the opposite direction. Also, the y- and z-components of the electric field E is higher than the x-component of E (Figure 1), so the effect of the rotation around y is larger.

Absorption: specific absorption rate

In this section simulations of the SAR for homogeneous muscle tissue surrounding the capsule are investigated. Basic restrictions to protect the public from exposure to electromagnetic fields are defined in ICNIRP [22], namely, a maximum of 2 W/kg is allowed in 10 g of tissue (in the head and trunk). SAR (watt per kilogram) is defined as the rate at which energy is absorbed by the body when it is exposed to a radio frequency (RF) electromagnetic field. Compliance with the ICNIRP guidelines is investigated for the 10 g localized SAR [22]. The maximum allowed radiated power in the MICS band is 25 μ W [23]. Figure 9a shows the peak spatial SAR (psaSAR) for the spiral when it is moved horizontally as a function of the depth inside the tissue. Also, the psaSARs for heterogeneous tissues (adult and child) are shown (Figure 9b, see further). The highest values occur near tissue surface due to the proximity of the interface muscle-air. The values in Figure 9 are considerably lower than the ICNIRP basic restrictions (about 1,000 times lower than 2 W/kg) [22]. Moreover, as the worst case, one can determine the maximum possible absorption, i.e., assuming that all power is absorbed in 10 g tissue with a maximum radiated power of 25 μ W. In that case, the psaSAR would be 2.5 mW/kg which is still below the ICNIRP basic restriction for localized absorption.

Figure 9
figure 9

Peak spatial average SAR (10 g) of the transmitting spiral antenna. (a) Homogeneous muscle versus depth. (b) Heterogeneous tissues of the adult and child models along the samples of the digestive tract.

Path loss for heterogeneous phantom models

Path loss models

Figure 10 compares the simulated PL in two realistic human body models with the PL in homogeneous tissues for different separations. A comparison between PL results of the adult and obese adult man will be made further. Figure 10 shows that of course different PL values can occur at a certain transmitter Tx- receiver Rx separation for different locations throughout the digestive tract (crosses for adult and circles for child in Figure 10): The capsule travels in the heterogeneous models along a tract through the pharynx, the esophagus, the stomach lumen, and the small and large intestines’ lumen. Moreover, misalignments between Tx and Rx antennas occur. In general, the PL increases with the distance between antennas for heterogeneous tissues. The slope of simulated PL in the realistic human body models is clearly higher than for the PL in homogenous tissues due to the changes in the characteristic impedances of the different tissues and misalignment situations when traveling along the digestive tract.

Figure 10
figure 10

Path loss for homogeneous and heterogeneous tissues in adult and child and corresponding regression models. Distance dipole-body of 18.5 cm for adult and obese model, Figure 2a; distance dipole-body of 13.5 cm for child model, Figure 2b.

Figure 10 shows that the path loss values for Duke (adult) are higher than the path loss values for Thelonius (child). This is due to the position of the dipole antenna (see Section ‘Configurations’), since for the child Thelonius it is placed in front of the body and for the adult Duke it is positioned at one side with the arm between the two antennas. The tissues in the arm add additional losses. Also the distance between body and dipole is smaller for Thelonius (13.5 cm) than for Duke (18.5 cm). The path loss for misalignment in the homogeneous esophagus tissue can be considered as the worst case, as the PL values are higher than those for the adult man configuration.

Table 2 summarizes for n and PL0 values obtained using linear regression fitting (Equation 2). The PL exponents for Thelonius and Duke are similar and about 7 to 8 in Table 2. In the heterogeneous tissues, the path loss exponent is higher than the one in homogeneous tissues (about equal to 3) because of the influence of the surrounding tissues and the mixture of alignment and misalignment situations. The path loss is considerably higher when the antennas are misaligned (doubling of the path loss exponent n and shift of PL0,dB of 7 dB when misaligned for the esophagus). The regression models for the heterogeneous phantoms have R2 values (a coefficient of determination) of about 0.7, which is good. An F-test concluded that the regression is significant, i.e., n≠0, at the 5% significance level (F=78−81, p<10−9). Standard deviations of 2.0 and 3.0 dB for the child and adult model are obtained, respectively. Finally, Table 2 shows that larger standard deviations σ correspond with lower R2 values. These regression models can be used for link budget calculations for in-to-out body communications.

Link budgets

Because of the proximity of the human body, antennas cannot be separated from the wireless propagation loss. Therefore, using the method of [28], one can calculate the maximum allowable path loss for sensor modules operating in the MICS band. With the maximum permitted level of −16 dBm EIRP (equivalent isotropically radiated power) or 25 μ W and a sensitivity level of −90 dBm for 152 kbps and −99 dBm for 51 kbps [29], a nominal maximum path loss (PLmax) of 74 dB for 152 kbps and 83 dB for 51 kbps is obtained, respectively. When comparing these maximum allowable path losses with the path loss models obtained in Figure 10, one can conclude that up to 400-mm separation wireless communication for the heterogeneous phantoms (adult and child) is possible for both data rates for the considered configurations (for the adult configuration higher separations can be difficult). However, for misalignment in the esophagus tissue, separations up to about 293 mm are possible for 152 kbps. The provided models of Table 2 can be used for further link budget calculations accounting for misalignment and rotation of the endoscopy capsule. To specifically account for the rotation, one can add a margin of 4 dB (x-axis) or 10 dB (y-axis) in the link budget. Also the application of the model with misaligned antennas is a possibility. A rotation of the capsule can result in a variation of the path loss up to 14 dB (10 and 4 dB margins).

Comparison of path loss for adult and obese adult men

Figure 10 also compares the obese human model (Fats) with the other tissues. In general, larger path loss is observed in the obese model due to the larger separations between transmit and receive antenna and the larger distance the electromagnetic waves have to propagate in the lossy human body tissue. We remark that a comparison of the PL in two human body models purely on the basis of the separation distance is not straightforward: for the same separation in Duke and Fats, the endoscopy capsule in Fats can be horizontally aligned with the dipole outside the human body and, thus, no misalignment loss is present. But in the Duke, the capsule will be positioned somewhere else in the body; the endoscopy capsule and dipole outside the body will not be horizontally aligned and misalignment loss occurs, which can result in a larger PL than for the obese model. Moreover, in the particular cases of Duke and Fats, when the dipole and the capsule are horizontally aligned, the propagation distance of the electromagnetic waves through the arm of Duke is about 2 cm longer, because near the wrists the arm of Fats is 2 cm smaller than the arm of Duke.

The mean and the maximum path loss in Fats equals to 70 and 82 dB, respectively. With respect to the adult this is 64 and 76 dB. This analysis shows that one has to be careful when making link budget evaluations: communication is possible for Fats for the considered configuration of 51 kbps.

Human absorption

Figure 9b shows also the psaSAR for the adult and child human body models (heterogeneous tissues) along the samples of the digestive tract. There are of course more samples for the adult (Duke) than for the child (Thelonius) because of the larger dimensions of the adult and thus longer tract. The absorption values are averaged in 10-g mass for an input power of 25 μ W. PsaSAR values for both phantoms are similar and compliant with the ICNIRP guidelines is obtained (psaSAR 10 g values are below 2 W/kg). The highest values are about 2.2 mW/kg for the maximum allowed transmission power of 25 μ W. Figure 9a,b has the same scale, enabling visual comparison. The absorption values in heterogeneous tissues are comparable (slightly higher maximum) with the absorptions for the homogeneous muscle tissue. Peaks for the heterogeneous models occur due to the proximity of tissue boundaries.


Path loss and absorption of an in-to-out body radio frequency (RF) wireless link between an endoscopy capsule and a receiver outside the body are numerically investigated. Three relevant homogeneous tissues (muscle tissue, skin tissue, and esophagus) and three heterogeneous human body models of an adult, obese adult, and a child are considered. A spiral antenna in the endoscopy capsule is tuned to operate in the MICS band at 402 MHz accounting for the properties of the human body. The misalignment between antennas causes an increase of the path loss exponent from 3 to 7 and an additional shift of 7 dB in the esophagus tissue. An increase in the path loss due to the rotation of the antenna up to 10 dB is observed. Path loss models for different homogeneous tissues and two realistic human body models are provided, enabling manufacturers to evaluate the performance of in-body to out-body WBAN systems. Path loss exponents in heterogeneous models are about 7 to 8 and higher than for homogeneous tissues. The obtained absorption values are around 2.2 mW/kg for the maximum allowed transmission power in the MICS band, which is about 1,000 times lower than the ICNIRP guidelines for localized absorption both in homogeneous and heterogeneous tissues. In this paper three realistic heterogeneous phantom models are investigated. As there are many variations among people, future research should account for morphology.

Authors’ information

WJ is a post-doctoral fellow of the FWO-V (Research Foundation - Flanders).


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This research is partly funded by the Fund for Scientific Research - Flanders (FWO-V, Belgium) project G.0049.09N.

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Correspondence to Wout Joseph.

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The authors declare that they have no competing interests.

Karen Lopez-Linares Roman, Günter Vermeeren contributed equally to this work.

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Lopez-Linares Roman, K., Vermeeren, G., Thielens, A. et al. Characterization of path loss and absorption for a wireless radio frequency link between an in-body endoscopy capsule and a receiver outside the body. J Wireless Com Network 2014, 21 (2014).

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  • In-to-out body
  • Heterogeneous human body model
  • Wireless body area network
  • Path loss
  • Propagation channel
  • Endoscopy capsule