Compact Wearable Meta Materials Antennas for Energy Harvesting Systems, Medical and IOT Systems

Demand for green technologies and green energy is in continuous growth in the last decade. Compact efficient radiators are very important for energy harvesting portable systems. Small antennas have low efficiency. The efficiency of communication and energy harvesting systems may increase by using efficient passive and active antennas. The system dynamic range may be improved by connecting amplifiers to the printed antenna feed line. Design, design considerations, computed and measured results of wearable meta-materials antennas with high efficiency for energy harvesting applications are presented in this paper. The antennas electrical parameters on human body were analyzed by using commercial full-wave software. The wearable antennas are compact and flexible and are 1.6 mm thick. The directivity and gain of the antennas with Split-ring resonators (SRR), is higher by 2 dB to 3 dB than the antennas without SRR. The resonant frequency of the antennas without SRR is higher by 5% to 10% than the antennas with SRR.


Introduction
Wearable medical, 5G and IOT systems cannot function without using batteries and power cords. Energy harvesting systems may eliminate both the need to replace batteries every day and the usage of power cords. In order to harvest as much free space electromagnetic energy as possible, it is important to collect the electromagnetic energy from several communication systems. Due to low RF power densities, efficient antennas are crucial. Several methods to produce green electricity from light, heat, radio waves and vibration have been developed [1][2][3]. Several printed antennas were employed for harvesting energy applications [1][2][3][4][5][6]. Patch and other printed antennas are used in RF Body Area Network (BAN), communication and medical systems . However, compact printed antennas such as these have low efficiency. Compact wearable devices and antennas have been presented in several papers in the last decade, see [1][2][3][4][5]. Meta material structures may be used to design compact antennas with high efficiency for wearable systems and energy harvesting systems, [6][7][8][9][10][11][12][13][14][15]. Meta material is a periodic material that derives its properties from the material structure rather than from its components. Periodic split ring resonators (SRRs) and metallic posts structures may be used to design materials with specific dielectric constant and permeability as presented in [6][7][8][9][10][11][12][13][14][15]. For example, artificial materials with negative dielectric permittivity were presented in [6]. A quasi-analytical and self-consistent model to compute the polarizabilities of split ring resonators (SRRs) is presented in [8]. An experimental setup is also proposed for measuring the magnetic polarizability of SRR structures. Experimental data are compared with theoretical results computed following the proposed model as presented in [8]. The design of a novel compact microstrip patch antenna whose size is reduced via the use of metamaterials is presented in [11]. However, the authors claim that the bandwidth and

Energy Harvesting Systems
There is a significant increase in the amount of electromagnetic energy in the air in the last decade. In electromagnetic energy harvesting systems, radio waves propagating in free space are captured, stored and used as green energy to charge batteries, amongst other purposes. The amount of RF waves in the air in 2013 was around 1.5 Exa-bytes per month. In comparison, the amount of RF waves in the air in 2017 was 11 Exa-bytes per month. In the last decade, there has been a continuous increase in RF traffic in the air. However, the amount of RF energy does not always correlate with the data. In 2010, one could perform fifteen million computations per KWh. In 2019, one can perform more computations per KWh. Modern communication devices consume more energy and need to be charged frequently. Commercial communication systems operate in the frequencies from 700 MHz to 2700MHz. Medical systems operate in the frequencies from 200 MHz to 1200MHz. WLAN systems operate in the frequencies from 5.2 GHz to 6 GHz. One may collect electromagnetic energy from 0.2 GHz up to 6 GHz. Energy sources used in harvesting systems are listed in Table 1. Harvested energy from indoor microwave energy sources is around 0.1 µW/cm 2 . Harvested power from RF energy sources in malls and stadiums may increase to around 1mW/cm 2 . RF energy is inversely proportional to distance and therefore decreases as the distance from the source is increased. The harvesting energy system operates as a dual mode energy harvesting system that can charge the battery when the switch is connected to the harvesting system. The receiving system employs a low noise amplifier to improve the system SNR. The Low Noise Amplifier (LNA), DC bias voltages are supplied by the receiving system DC unit and then supplied continuously to the system. The energy harvesting system consists of radiator, a rectifying circuit and a rechargeable battery, as presented in Figure 1. Electromagnetic AC energy is converted to direct current by using a rectifier that may be a half-wave or a full-wave rectifier. A half-wave voltage rectifier is shown in Figure 2. A half-wave   The ripple voltage is given in Equation (2). T, the wave period time, should be greater than the time constant , where ≪ .
The rectifier output voltage is flattened by connecting a capacitor in shunt to the resistor as presented in Figure 3. The half-wave rectifier efficiency is 40.6%, as given in Equation (3). DC power supplies uses diode bridge full-wave rectifier that consists of four diodes. D1 through D4, as shown in in Figure 4, connected to form a bridge. During the positive input half cycle, terminal A will be positive and terminal B will be negative. Diodes D1 and D2 will become forward biased and D3 and D4 will be reverse biased. A capacitor is used to improve the flatness of the rectifier output voltage variation as function of time, as shown in Figure 5. The capacitor can be a voltage-controlled diode, varactor. Varactors are voltage variable capacitors designed to provide electronic tuning of electrical devices. The output voltage ripple (see Equation (2)) of the improved rectifier may be tuned as a function of the frequency of the received signal or of the load resistance, R. The varactor bias voltage is varied automatically to get the lowest output voltage ripple. The rectifier output DC voltage The rectifier output voltage may be improved by connecting a capacitor in shunt to the resistor.  The ripple voltage is given in Equation (2). T, the wave period time, should be greater than the time constant , where ≪ .
The rectifier output voltage is flattened by connecting a capacitor in shunt to the resistor as presented in Figure 3. The half-wave rectifier efficiency is 40.6%, as given in Equation (3). DC power supplies uses diode bridge full-wave rectifier that consists of four diodes. D1 through D4, as shown in in Figure 4, connected to form a bridge. During the positive input half cycle, terminal A will be positive and terminal B will be negative. Diodes D1 and D2 will become forward biased and D3 and D4 will be reverse biased. A capacitor is used to improve the flatness of the rectifier output voltage variation as function of time, as shown in Figure 5. The capacitor can be a voltage-controlled diode, varactor. Varactors are voltage variable capacitors designed to provide electronic tuning of electrical devices. The output voltage ripple (see Equation (2)) of the improved rectifier may be tuned as a function of the frequency of the received signal or of the load resistance, R. The varactor bias voltage is varied automatically to get the lowest output voltage ripple. The rectifier output DC voltage DC output power AC input power 2 The rectifier output voltage may be improved by connecting a capacitor in shunt to the resistor. The ripple voltage is given in Equation (2). T, the wave period time, should be greater than the time constant τ, where τ = RC T.
The rectifier output voltage is flattened by connecting a capacitor in shunt to the resistor as presented in Figure 3. The half-wave rectifier efficiency is 40.6%, as given in Equation (3). DC power supplies uses diode bridge full-wave rectifier that consists of four diodes. D1 through D4, as shown in in Figure 4, connected to form a bridge. During the positive input half cycle, terminal A will be positive and terminal B will be negative. Diodes D1 and D2 will become forward biased and D3 and D4 will be reverse biased. A capacitor is used to improve the flatness of the rectifier output voltage variation as function of time, as shown in Figure 5. The capacitor can be a voltage-controlled diode, varactor. Varactors are voltage variable capacitors designed to provide electronic tuning of electrical devices. The output voltage ripple (see Equation (2)) of the improved rectifier may be tuned as a function of the frequency of the received signal or of the load resistance, R. The varactor bias voltage is varied automatically to get the lowest output voltage ripple. The rectifier output DC voltage The rectifier output voltage may be improved by connecting a capacitor in shunt to the resistor.    The full wave rectifier efficiency is 81.2% as presented in Equation (4). The diode in the rectifier circuit can be a Schottky diode. Schottky diodes are semiconductor diodes that have a fast switching action and a low forward voltage drop. Usually the voltage drops from 0.2 V to 0.4 V across the diode terminals, when current flows through the diode. This lower voltage drop provides higher switching speed and better system efficiency. A wearable harvesting system and a wearable battery charger attached to the patient shirt are presented in Figure 6.   The full wave rectifier efficiency is 81.2% as presented in Equation (4). The diode in the rectifier circuit can be a Schottky diode. Schottky diodes are semiconductor diodes that have a fast switching action and a low forward voltage drop. Usually the voltage drops from 0.2 V to 0.4 V across the diode terminals, when current flows through the diode. This lower voltage drop provides higher switching speed and better system efficiency. A wearable harvesting system and a wearable battery charger attached to the patient shirt are presented in Figure 6.    The full wave rectifier efficiency is 81.2% as presented in Equation (4). The diode in the rectifier circuit can be a Schottky diode. Schottky diodes are semiconductor diodes that have a fast switching action and a low forward voltage drop. Usually the voltage drops from 0.2 V to 0.4 V across the diode terminals, when current flows through the diode. This lower voltage drop provides higher switching speed and better system efficiency. A wearable harvesting system and a wearable battery charger attached to the patient shirt are presented in Figure 6. The full wave rectifier efficiency is 81.2% as presented in Equation (4). The diode in the rectifier circuit can be a Schottky diode. Schottky diodes are semiconductor diodes that have a fast switching action and a low forward voltage drop. Usually the voltage drops from 0.2 V to 0.4 V across the diode terminals, when current flows through the diode. This lower voltage drop provides higher switching speed and better system efficiency. A wearable harvesting system and a wearable battery charger attached to the patient shirt are presented in Figure 6.

Wearable Antenna with SRR and Metallic Strips
A dual polarized antenna with SRR and metallic strips is presented in Figure 7. The flexible wearable antenna dimensions are 19.8 × 4 × 0.16 cm. The antenna was printed on RT Duroid 5880 with dielectric constant of 2.2. The dipole feed network and metallic strips are printed on the first layer. The radiating dipole with SRR is printed on the second layer. The thickness of each layer is 0.8 mm. The printed dipole with SRR is horizontal polarized. The slot antenna is vertical polarized. The dipole and the slot antenna create dual polarized antenna. The resonant frequency of the antenna with SRR is around 330 MHz. The resonant frequency of the antenna without SRR is 10% higher. The computed S11 and antenna gain are presented in Figure 8. The antenna bandwidth is around 46% for VSWR better than 3:1. The spherical computed radiation pattern is shown in Figure 9. Maximum radiation is in the z axis direction. Directivity and gain of the antenna with SRR are around 5.5 dBi as shown in Figure 10. The feed network of the antenna in Figure 7 was optimized to yield VSWR better than 2.5:1 in frequency range of 250 MHz to 420 MHz as shown in Figure 11. The SRR have an important role in the radiation characteristics of the antenna. The antenna with SRR and metallic strips was optimized and more stubs and metallic strips were added to yield wider bandwidth as shown in Figure 12. The reflection coefficient, S11, of the modified antenna with metallic strips and SRR is presented in Figure 13. The antenna bandwidth is around 65% for VSWR better than 3:1. The antenna beam width is around 100°.

Slot
Strips Stubs

Wearable Antenna with SRR and Metallic Strips
A dual polarized antenna with SRR and metallic strips is presented in Figure 7. The flexible wearable antenna dimensions are 19.8 × 4 × 0.16 cm. The antenna was printed on RT Duroid 5880 with dielectric constant of 2.2. The dipole feed network and metallic strips are printed on the first layer. The radiating dipole with SRR is printed on the second layer. The thickness of each layer is 0.8 mm. The printed dipole with SRR is horizontal polarized. The slot antenna is vertical polarized. The dipole and the slot antenna create dual polarized antenna. The resonant frequency of the antenna with SRR is around 330 MHz. The resonant frequency of the antenna without SRR is 10% higher. The computed S11 and antenna gain are presented in Figure 8. The antenna bandwidth is around 46% for VSWR better than 3:1. The spherical computed radiation pattern is shown in Figure 9. Maximum radiation is in the z axis direction. Directivity and gain of the antenna with SRR are around 5.5 dBi as shown in Figure 10. The feed network of the antenna in Figure 7 was optimized to yield VSWR better than 2.5:1 in frequency range of 250 MHz to 420 MHz as shown in Figure 11. The SRR have an important role in the radiation characteristics of the antenna. The antenna with SRR and metallic strips was optimized and more stubs and metallic strips were added to yield wider bandwidth as shown in Figure 12. The reflection coefficient, S11, of the modified antenna with metallic strips and SRR is presented in Figure 13. The antenna bandwidth is around 65% for VSWR better than 3:1. The antenna beam width is around 100 • .

Wearable Antenna with SRR and Metallic Strips
A dual polarized antenna with SRR and metallic strips is presented in Figure 7. The flexible wearable antenna dimensions are 19.8 × 4 × 0.16 cm. The antenna was printed on RT Duroid 5880 with dielectric constant of 2.2. The dipole feed network and metallic strips are printed on the first layer. The radiating dipole with SRR is printed on the second layer. The thickness of each layer is 0.8 mm. The printed dipole with SRR is horizontal polarized. The slot antenna is vertical polarized. The dipole and the slot antenna create dual polarized antenna. The resonant frequency of the antenna with SRR is around 330 MHz. The resonant frequency of the antenna without SRR is 10% higher. The computed S11 and antenna gain are presented in Figure 8. The antenna bandwidth is around 46% for VSWR better than 3:1. The spherical computed radiation pattern is shown in Figure 9. Maximum radiation is in the z axis direction. Directivity and gain of the antenna with SRR are around 5.5 dBi as shown in Figure 10. The feed network of the antenna in Figure 7 was optimized to yield VSWR better than 2.5:1 in frequency range of 250 MHz to 420 MHz as shown in Figure 11. The SRR have an important role in the radiation characteristics of the antenna. The antenna with SRR and metallic strips was optimized and more stubs and metallic strips were added to yield wider bandwidth as shown in Figure 12. The reflection coefficient, S11, of the modified antenna with metallic strips and SRR is presented in Figure 13. The antenna bandwidth is around 65% for VSWR better than 3:1. The antenna beam width is around 100°.    Comparison between antennas with and without SRR is given in Table 2. The measured results agree with the computed results.   Comparison between antennas with and without SRR is given in Table 2. The measured results agree with the computed results.  Comparison between antennas with and without SRR is given in Table 2. The measured results agree with the computed results.   Comparison between antennas with and without SRR is given in Table 2. The measured results agree with the computed results.   [dB] S11 S11 Free space radiation

Slot New Strips New Stubs
MHz S11   [dB] S11 S11 Free space radiation

Slot New Strips New Stubs
MHz S11   [dB] S11 S11 Free space radiation

Slot New Strips New Stubs
MHz S11 Figure 13. S11 for antenna with metallic strips.

Metamaterial Antennas in Vicinity to the Patient Body
The metamaterial antennas S11 variation near the patient body were computed by using the structure presented in Figure 14a. Dielectric constant and conductivity of human body tissues are given in Table 3 [15]. The antenna location on the human body is considered by computing S11 for different dielectric constant and conductivity of the body tissues. The variation of the of body tissues dielectric constant from five at fat tissues to 43 at the stomach area, and to 63 at muscle tissues, shifts the antenna resonant frequency by 2% to 5%. The antenna was inserted inside a belt as shown in Figure 14b. The belt thickness was varied from 1 to 4 mm. The belt dielectric constant was varied from 2 to 4. The antennas impedance was computed and measured for air spacing of 0mm to 10mm, between the antennas and patient shirt. Table 3. Electrical properties of body tissues [16,17].

Tissue
Property 435MHz 605MHz 995MHz  The dielectric constant of the patient shirt was varied from 2.2 to 4.2. Figure 15 presents S11 results of the antennas with SRR and metallic strips. The antenna resonant frequency was shifted by 1% to 3%. Results presented in Figure 15 indicate that these antennas have VSWR better than 3:1 for 65% bandwidth. The radiation pattern of the antennas with metallic strips and SRR on human body is shown in Figure 16. S11 results for different belt thickness, shirt thickness and air spacing between the antennas and human body, for the antennas without SRR, are shown in Figure 17. One may conclude from results shown in Figure 17 that the antenna has S11 better than -9 dB for air spacing  The dielectric constant of the patient shirt was varied from 2.2 to 4.2. Figure 15 presents S11 results of the antennas with SRR and metallic strips. The antenna resonant frequency was shifted by 1% to 3%. Results presented in Figure 15 indicate that these antennas have VSWR better than 3:1 for 65% bandwidth. The radiation pattern of the antennas with metallic strips and SRR on human body is shown in Figure 16. S11 results for different belt thickness, shirt thickness and air spacing between the antennas and human body, for the antennas without SRR, are shown in Figure 17. One may conclude from results shown in Figure 17 that the antenna has S11 better than -9 dB for air spacing up to 10 mm between the antennas and the human body. The dielectric constant of the patient shirt was varied from 2.2 to 4.2. Figure 15 presents S11 results of the antennas with SRR and metallic strips. The antenna resonant frequency was shifted by 1% to 3%. Results presented in Figure 15 indicate that these antennas have VSWR better than 3:1 for 65% bandwidth. The radiation pattern of the antennas with metallic strips and SRR on human body is shown in Figure 16. S11 results for different belt thickness, shirt thickness and air spacing between the antennas and human body, for the antennas without SRR, are shown in Figure 17. One may conclude from results shown in Figure 17 that the antenna has S11 better than -9 dB for air spacing up to 10 mm between the antennas and the human body. MHz S11 Figure 15. Antennas with SRR S11 results on a patient.  Figure 13 on the human body.
The antenna belt is attached to the patient's body. The cable from each antenna is connected to the medical system.

Wearable Harvesting System.
The proposed meta materials antennas may be placed on the patient's body as shown in Figure  18, which presents a medical monitoring health system with wearable antennas. The received signals are combined by a power combiner and transferred via a switch to the receiver and to the harvesting system, as presented in Figure 19. In several wearable systems the distance separating the transmitting and receiving antennas is in the near field zone. In the near-field area the antennas are magnetically coupled and only near field effects should be considered. The antennas electrical characteristics on human body may be measured by using a phantom that represents the electrical properties of the human body, as presented in [5].  Figure 13 on the human body.
The antenna belt is attached to the patient's body. The cable from each antenna is connected to the medical system.   Figure 13 on the human body.
The antenna belt is attached to the patient's body. The cable from each antenna is connected to the medical system.

Wearable Harvesting System.
The proposed meta materials antennas may be placed on the patient's body as shown in Figure  18, which presents a medical monitoring health system with wearable antennas. The received signals are combined by a power combiner and transferred via a switch to the receiver and to the harvesting system, as presented in Figure 19. In several wearable systems the distance separating the transmitting and receiving antennas is in the near field zone. In the near-field area the antennas are magnetically coupled and only near field effects should be considered. The antennas electrical characteristics on human body may be measured by using a phantom that represents the electrical properties of the human body, as presented in [5].

Wearable Harvesting System
The proposed meta materials antennas may be placed on the patient's body as shown in Figure 18, which presents a medical monitoring health system with wearable antennas. The received signals are combined by a power combiner and transferred via a switch to the receiver and to the harvesting system, as presented in Figure 19. In several wearable systems the distance separating the transmitting and receiving antennas is in the near field zone. In the near-field area the antennas are magnetically coupled and only near field effects should be considered. The antennas electrical characteristics on human body may be measured by using a phantom that represents the electrical properties of the human body, as presented in [5].   Figure 19 presents a basic receiver block diagram. Receiving active antenna layout is shown in Figure 20. A matching network matches the antenna with SRR to the LNA. The LNA, is a high linearity gain block amplifier. At 1.9 GHz, the amplifier typically provides a 14dB gain. These   Figure 19 presents a basic receiver block diagram. Receiving active antenna layout is shown in Figure 20. A matching network matches the antenna with SRR to the LNA. The LNA, is a high linearity gain block amplifier. At 1.9 GHz, the amplifier typically provides a 14dB gain. These  Figure 19 presents a basic receiver block diagram. Receiving active antenna layout is shown in Figure 20. A matching network matches the antenna with SRR to the LNA. The LNA, is a high linearity gain block amplifier. At 1.9 GHz, the amplifier typically provides a 14dB gain. These antennas also function as transmitting antennas. The LNA output P1dB is 20 dBm. The LNA Noise Figure is 1.8dB. An output matching network matches the amplifier to the receiver. A DC bias network supplies the required voltages to the amplifiers. The active receiving meta materials antenna gain is 11+2 dB from 150 MHz to 900 MHz as shown in Figure 21.   A photo of the feed network and metallic strips is shown in Figure 22a. A photo of antenna with SRR is shown in Figure 22b. A comparison of electrical parameters of compact wearable antennas for medical, 5G and IOT systems is listed in Table 4. Printed dipole with and without SRR were presented in [1]. Results listed in Table 4 show that the gain of printed dipole with SRR is 3 dB higher than the printed dipole without SRR. Wideband passive and active slot antennas were presented in [1].An Enhancement PHEMT, Pseudo morphic High Electron Mobility Transistor, LNA was connected to the antenna, as shown in Figure 22    A photo of the feed network and metallic strips is shown in Figure 22a. A photo of antenna with SRR is shown in Figure 22b. A comparison of electrical parameters of compact wearable antennas for medical, 5G and IOT systems is listed in Table 4. Printed dipole with and without SRR were presented in [1]. Results listed in Table 4 show that the gain of printed dipole with SRR is 3 dB higher than the printed dipole without SRR. Wideband passive and active slot antennas were presented in [1].An Enhancement PHEMT, Pseudo morphic High Electron Mobility Transistor, LNA was connected to the antenna, as shown in Figure 22. At 2 GHz, the amplifier has an 18dB gain. The LNA output P1dB is 19 dBm. The LNA Noise Figure is   A photo of the feed network and metallic strips is shown in Figure 22a. A photo of antenna with SRR is shown in Figure 22b. A comparison of electrical parameters of compact wearable antennas for medical, 5G and IOT systems is listed in Table 4. Printed dipole with and without SRR were presented in [1]. Results listed in Table 4 show that the gain of printed dipole with SRR is 3 dB higher than the printed dipole without SRR. Wideband passive and active slot antennas were presented in [1]. An Enhancement PHEMT, Pseudo morphic High Electron Mobility Transistor, LNA was connected to the antenna, as shown in Figure 22. At 2 GHz, the amplifier has an 18dB gain. The LNA output P1dB is 19 dBm. The LNA Noise Figure is      The harvesting energy system operates as a dual mode energy harvesting system that can charge the battery when the switch is connected to the harvesting system. At standby mode of the communication system, the switch disconnects the receiver and connects the harvesting system to the active antenna. The harvesting system efficiency increases as function of the RF input power to the harvesting system as listed in Table 5. The amplifier amplifies the input power at the input of the energy harvesting system and improves the efficiency of the harvesting system. Results listed in Table 5 are also presented by companies that manufacture commercial RF energy harvesting systems.

Conclusions
Compact flexible antennas with high efficiency for medical and IOT systems were developed by employing meta material structures. Wideband, small, wearable, passive and active energy harvesting systems and antennas in frequencies ranging from 0.1 GHz to 1 GHz are presented in this paper. The antennas are placed in a belt and may be used to measure the patient's medical health. The wearable antennas are compact and can be attached to the body. The antennas also allow the patient's easy movement (running, jumping and working). The electromagnetic energy is converted to DC energy that may be employed to charge batteries, wearable medical devices and commercial Body Area Networks (BANs). A new class of wideband printed meta materials antennas with high efficiency is presented. The bandwidth of the antenna with SRR and metallic strips is around 65% for VSWR better than 3:1. Optimization of the antenna feed network, number of the coupling stubs, SRR configuration and the location of the metallic strips may be used to tune the antenna resonant frequency, radiation characteristics and the antenna bandwidth. The length of the antennas without SRR is 10% higher than the antennas with SRR. The resonant frequency of the antennas without SRR is 5-10% higher than the antennas with SRR. The gain and directivity of the wearable antennas with SRR is up to 3 dB higher than the antennas without SRR. The measured results agree with computed results.
Usually harvested power from RF transmitting links at crowded places, malls and stadiums, is around 1 mW/cm 2 . The harvesting energy system operates as a Dual Mode Energy harvesting system that can charge the battery when the switch is connected to the harvesting system in standby mode. Usually the switch is connected to the receiving system. The receiving system employs an LNA to improve the system SNR. The LNA DC bias voltages are supplied by the receiving system DC unit. The harvesting system efficiency increases as function of the RF input power to the harvesting system. These results are also presented by companies that manufacture commercial RF energy harvesting systems.
Harvesting system efficiency and dynamic range may be improved by using active antennas. All antennas presented in this paper can function as passive and active antennas.