# A Low-Profile Compact Meander Line Telemetry Antenna with Low SAR for Medical Applications

Authors: N. H. Sulaiman; Muhammad Inam Abbasi; N. A. Samsuri; M. K. A. Rahim; F. C. Seman
Journal: Wireless Communications and Mobile Computing
 (2022)

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## Abstract

A low-profile Compact Meander Line Telemetry Antenna (CMLTA) operating at 402.5 MHz for the Medical Implant Communication System (MICS) band medical applications is introduced. The proposed antenna focuses specifically on pacemaker telemetry applications. The meander line technique with an open loop configuration and simple transmission line feeding mechanism has been used for achieving the compact design. Based on the theory of surface current distribution, the proposed technique provides the opportunity to increase the electrical dimensions while decreasing the physical dimensions of the antenna. Further design optimization is carried out to optimize the overall antenna size to a maximum volume of 4080 mm3. By introducing CMLTA, the size of the antenna is reduced by 79% as compared to the previous work. The proposed antenna demonstrated satisfactory performance with 10 dB bandwidth of 6.17%, a maximum gain of -22 dBi and an EIRP of -25.28 dBi. The analysis of Specific Absorption Rate under premise use of 1 W input power provided the maximum 1 g and averaged 10 g SAR of 74.7 W/kg and 17.7 W/kg, respectively, demonstrating a satisfactory level according to the IEEE standard safety guidelines. Fabrication and measurements are carried out where measured results are found to be in good agreement with the simulated results. With the optimized dimensions, satisfactory gain, EIRP, and SAR performance, the proposed CMLTA is deemed suitable for pacemaker telemetry applications for effective communication.


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## Body

## 1. Introduction

The microstrip patch antennas are proposed by different researchers in various forms because of their compact size and high-performance capabilities. Many applications require high gain antennas, and hence, microstrip arrays are required for these applications [1–6], while other applications demand electrically small and compact antennas [7, 8]. The implantable antenna is one of its kind, which has been receiving immense attention nowadays [9–14]. Recent research works have shown that implantable antenna needs to be designed with broadband performance in order to reduce the shift in resonant frequency due to nonhomogenous human tissues [15]. The antenna size is one of the main issues in designing an implantable antenna. Besides that, maintaining good performance in different environments is indeed a challenging task. Some solutions have been suggested in the past, such as loading the ground plane with slots [16]. However, slotted ground design is confined to those applications without a conductor under the ground plane. Two more types of low-profile implantable antennas were introduced in [17], where spiral and PIFA structures were proposed to obtain a small size for implantable antennas. The radiation efficiency of PIFA was observed to be higher than that of the microstrip antenna. However, PIFA in [17] used high dielectric permittivity material to obtain a smaller size. In another work [18], an implantable antenna for pacemaker applications with dimensions of 42×43.6×11mm was proposed, and the investigations were carried out by implanting the antenna inside the pig. However, the accuracy of measured results and antenna size still remains the major issue to be resolved in implantable antenna design.Since an implantable antenna has to be embedded in the human body, therefore, safety considerations have to be taken into account while designing such antennas. Moreover, the design process of biomedical systems involves Electromagnetic (EM) radiating structures like antennas, which might harm the human body by excessive exposure to radiation or thermal heating. Effective Isotropic Radiated Power (EIRP) is one of the factors that can be used to characterize and limit the radiated power from the antenna. The thermal heating of the tissues can be classified by the Specific Absorption Rate (SAR) [19, 20]. In order to preserve patient safety, the standard SAR guidelines need to be carefully addressed. The antenna is required to be designed with accuracy and carefulness, considering it is surrounded by a complicated tissue environment [21, 22]. Generally, for implantable antenna measurements and analysis, there are two approaches used to mimic the human body, which are the one-layer skin tissues model (homogenous phantom) and three-layer model (non-homogenous phantom) consisting of skin, fat, and muscle [23, 24]. In [25], two tissue models were compared, and the results showed that there is no significant discrepancy between the reflection coefficient of the antenna, while a slight resonant frequency shift was observed. In another work, the implantable antenna was also analyzed in the human body by using Gustav Voxel model, which is available in CST MWS [9]. This technique can also be useful, particularly for determining the antenna performance according to the safety limit for EIRP and SAR.In this research work, an improved design of a low-profile implantable antenna based on the Compact Meander Line Telemetry Antenna (CMLTA) operating at 402.5 MHz for the Medical Implant Communication System (MICS) band medical applications is proposed. The antenna size has been reduced based on the optimization of the electrical length of the antenna, while the EIRP and SAR have been governed to follow the safety standards by the effective use of substrate and superstrate. The analysis is based on the measured results obtained using the developed single-layer homogeneous phantom model. The proposed CMLTA could be a suitable telemetry antenna to be implanted together with an artificial pacemaker.


## 2. Antenna Design and Optimization

The proposed antenna is designed at 402.5 MHz by means of commercially available CST Microwave Studio (CST MWS). Miniaturization of the implantable antenna is achieved by the optimization of the meander line technique as detailed in [26, 27]. Furthermore, open loop meander and closed loop meander line are also considered in the miniaturization process. The full ground plane configuration has been used, keeping in mind the requirements and sensitivity of the pacemaker telemetry applications. On the other hand, by introducing open loop configurations, the length and width of the substrate have been successfully reduced by 36.84% and 40%, respectively, as compared to the closed loop configuration. Design optimization of the antenna is carried out in order to achieve the optimum size and obtain efficient performance by comparing closed loop and open loop CMLTA, as shown in Figure 1.Figure 1
Detail design process and configuration of the proposed CMLTA (open loop) (all dimensions are in mm).The comparison between the surface current distribution and reflection coefficient performance of closed loop and open loop CMLTA antennas is shown in Figure2(a). It can be observed from the figure that by implementing an open loop configuration, the surface current covers a longer distance, and hence, the electrical dimensions of the antenna are enlarged. This provides an opportunity to reduce the physical dimensions of the antenna. Figure 2(b) shows a comparison between the simulated return loss performance of open loop and closed loop meander line antennas. It has been demonstrated that open loop configuration offers higher bandwidth performance as compared to the closed loop configuration. Therefore, open loop configuration is chosen for further investigation in this work and annotated as Compact Meander Line Telemetry Antenna (CMLTA). Figure 2(c) shows the wave impedance of the proposed antenna, which was observed to be well matched at 402.5 MHz as in [28].Figure 2
Comparison between closed loop and open loop (CMLTA): (a) surface current distribution; (b) simulated return loss performance; (c) wave impedance of the proposed CMLTA.
(a)(b)(c)For further evaluation, the proposed CMLTA is also simulated in in-body environment. In this case, the CMLTA is added with the superstrate layer which is capable of protecting neighbouring body tissues surrounding the proposed antenna. The superstrate layer acts as a buffer between the metal radiator and human tissues by reducing Radio Frequency (RF) power at the locations of lossy human tissues [29]. Therefore, for the proposed design, the superstrate and substrate have been used. In order to obtain a low profile antenna, FR-4 substrate has been chosen due to the low cost and easy fabrication. Based on the investigations carried out for different available thicknesses of FR4, 3.2 mm is observed to provide good matching, optimum size and better bandwidth performance as compared to other thicknesses of the superstrate. The complete assembly of the proposed antenna consists of a substrate with the full ground on one side and a radiating element on the other side. The radiating meander line is covered with the superstrate, and the antenna is placed inside the plastic casing. Different materials for the casing were investigated, which include plastic, aluminium, and tin, while the optimum desired performance was achieved by using plastic casing, as demonstrated in [30].In order to investigate the performance of the proposed antenna inside the human body, simulations have been carried out in a nonhomogenous model as well as the Gustav body model made available by CST MWS as shown in Figure3.Figure 3
Simulations and measurements setup of the proposed antenna. (a) Simulation setup of the CMLTA in voxel body and (b) nonhomogenous phantom.For the nonhomogenous model, the CMLTA is embedded under the skin and above fat and muscle layers. As in [31], the skin thickness is varied between 1 mm to 5 mm in order to observe its effect on the antenna performance. The size of the proposed antenna has been optimized by implanting the antenna inside the human body environment. However, for measurement purposes, the CMLTA has also been simulated in a homogenous phantom (εr=59.95,tanδ=0.622). The size comparison of the proposed antenna with previous work is shown in Table 1, while the radiation pattern of the antenna is shown in Figure 4.Table 1
Size comparison between the proposed antenna and previous work.
Ref.ReferencesProposed CMLTAPercentage reductionDesign technique/materialVolume (mm3)Design techniqueVolume (mm3)[12]PIFA/ Taconic CER-10 (ɛr=10)20143Microstrip Meander Line/(FR4=4.7andtanδ=0.025)408079%[11]Microstrip Spiral/Rogers 3010 (ɛr=10.2)1024060%[11]PIFA/Rogers 3010 (ɛr=10.2)614434%Figure 4
Simulated radiation patterns for CMLTA in phantom (nonhomogenous), Gustav voxel, and free space.It can be observed that a good monopole-like far-field pattern can be achieved by the proposed antenna design. The maximum realized gains at 402.5 MHz in nonhomogenous phantom and Gustav voxel are -24 dBi and -22 dBi, respectively, which are considered suitable for pacemaker telemetry applications. Based on the IEEE guidelines for safety, the EIRP of the implantable antenna should be lesser than -16 dBm [31]. The EIRP of the proposed design is -25.28 dBm and -32.71 dBm for homogeneous phantom and Gustav voxel, as shown in Table 2.Table 2
G ain and EIRP of the proposed CMLTA.
Simulation environmentPeak gain (dBi)Power (mW)EIRP (dBm)Homogeneous phantom-240.745-25.28Nonhomogenous phantom-29.90.110-39.49Gustav voxel-220.085-32.71


## 3. Fabrication and Measurements

The Compact Meander Line Telemetry Antenna (CMLTA) has been fabricated using 3.2 mm thick FR-4 (ɛr=4.7,tanδ=0.025) dielectric substrate (both for substrate and superstrate). The width (Ws) and length (Ls) of the substrate are 30 mm and 21.25 mm, respectively. As discussed in a previous work [32], the implantable antenna has to be protected using a casing in order to avoid direct contact with the developed phantom. The proposed antenna has to be wrapped in plastic for measurement purposes so that the radiating element can be covered and direct contact with the liquid phantom can be avoided. If the wrapping is not proper, it will affect the RF signal; hence, the CMLTA performance will be degraded. The fabricated sample of the proposed CMLTA is shown in Figure 5.Figure 5
Fabricated antenna. (a) CMLTA on the substrate, (b) superstrate, (c) ground plane, and (d) CMLTA wrapped in plastic.
(a)(b)(c)(d)For measurement purposes, the homogenous liquid phantom has been successfully developed using the composition of water (51.3%), sugar (47.3%), and salt (1.4%) to achieve phantom properties at 402.5 MHz. Various composite samples of the solution have been developed to characterize material properties for comparison with the theoretical properties at 402.5 MHz [17]. Figure 6 shows the optimum dielectric properties achieved from the developed solution. The measured dielectric properties of the proposed solution have good agreement with theoretical values provided by FCC, with a maximum discrepancy of 0.43% in permittivity and 11.11% in conductivity. The obtained measured results are much closer to the FCC [33] values as compared to the results provided in the previously proposed phantom [34].Figure 6
Comparison between measured and theoretical material properties of the developed phantom.By using the developed phantomS11, measurements of the CMLTA have been carried out with a Vector Network Analyzer (VNA). The measurement setup is shown in Figure 7.Figure 7
Measurement setup of CMLTA in a homogeneous phantom.As depicted in Figure7, the CMLTA, wrapped in plastic, has been completely immersed in the developed liquid phantom. Moreover, it has been assured that the SMA connector is not having any contact with the phantom, which can modify the input impedance and hence can provide improper measured results. The comparison between the measured and simulated results is shown in Figure 8.Figure 8
Simulated (s) and measured (m) CMLTA performances.
It can be observed that the measured results are in good agreement with the simulated results, especially in the case of the phantom model. It can also be noted that the proposed implantable antenna worked well within the MICS band (402 MHz-405 MHz). The antenna in free space demonstrated a shift in resonant frequency as expected as the proposed antenna is purposely designed to be utilized in an in-body environment.


## 4. Specific Absorption Rate Analysis

In the simulation, the CMLTA is placed inside the Gustav body model, which consists of multiple layers of tissues such as muscle, skin, and fat. The CMLTA is implanted in between the skin tissue and muscle. The input power of 1 W is used, and the SAR distribution is as shown in Figure9.Figure 9
SAR distribution in Gustav model at 402.5 MHz (1 W input power).
(a)
10 g(b)
1 gThe maximum SAR is observed near the skin. No further penetration is observed as the CMLTA is equipped with a superstrate layer that protects the adjacent body tissue. Based on the previous studies, SAR investigations have also been carried out using 1 W as input power [35]. Under the premise of 1 W input power, the maximum of 10 g and 1 g average of SAR is 74.7 W/kg and 17.7 W/kg, respectively. Hence, to meet the 1 g and 10 g IEEE standards, the allowed input power of the CMLTA should be limited to 8.31 mW and 55.20 mW, respectively. The tabulated SAR results are shown in Table 3. In addition, the results are also recorded for different input power ranging from 0 dBm to 5 dBm (as the range of power is considered in [20]).Table 3
SAR of CMLTA.
StandardMaximum SAR (W/kg)Maximum input power (mW)C95.1-1999 (1 g-avg)74.78.31C95.1-2005 (10 g-avg)17.755.20In order to validate the simulations, measurements are conducted, and the measurement setup for SAR is shown in Figure10. The SAR probe from INDEXSAR is used to measure SAR using the CheckSar software interface. The fabricated CMLTA is connected to the signal generator. The CMLTA is immersed in the developed liquid phantom, and the input power is varied as in the simulation. The graphical results for SAR measurements and comparison with simulations for variable input power are shown in Figure 11.Figure 10
SAR measurements: (a) general measurement setup; (b) SAR measurements using liquid phantom.
(a)(b)Figure 11
Simulated and measured SAR using liquid phantom.It can be observed from Figure11 that by varying input power from 0 dBm to 5 dBm, peak SAR has increased from 1.11 W/kg to 3.50 W/kg. The increment of peak SAR follows the theoretical trend of SAR, where a higher SAR level is distributed with higher excited power due to more absorption of energy by the human body.Table4 outlines the performance comparison of the proposed CMLTA to different implantable antennas. It can be seen that the CMLTA offers 6.17% of bandwidth performance, which is in the same range as previous works. Moreover, in this work, peak gain and SAR performance have also been compared between voxel body and phantom muscles demonstrating much better SAR performance.Table 4
Performance comparisons of the proposed antenna and other implantable antennas.
Ref.10 dB-BW (%)Implantation tissuePeak gain (dBi)1 g-avg max SAR (W/kg)[36]8.37Skin—294[37]5.17Muscle—274.9[38]6.09Skin-33.2606CMLTA6.17Voxel body-2274.7


## 5. Conclusions

A Compact Meander Line Antenna (CMLTA) has been designed and developed for implantable medical applications. By employing the meander line technique, a CMLTA has been proposed where the overall dimensions have provided a 79% reduction as compared to the antenna designs provided by the previous researchers. Moreover, CMLTA is easier to fabricate and has a low-cost antenna. A homogenous phantom has also been developed for validation through measurements. The reflection coefficient orS11 is successfully investigated by using a developed phantom, and a peak gain of -22 dBi with an EIRP of -25.28 dBi is demonstrated. Moreover, SAR analysis of the proposed antenna is carried out where the maximum SAR value is observed to be 74.7 W/kg which satisfies the IEEE standard safety guidelines. In the future, the antenna will be further used for In-Vivo measurements in order to demonstrate its applicability in implantable medical applications.



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