Research Article | Open Access
Sara El-Molla, Andreas Albrecht, Engin Cagatay, Philipp Mittendorfer, Gordon Cheng, Paolo Lugli, José F. Salmerón, Almudena Rivadeneyra, "Integration of a Thin Film PDMS-Based Capacitive Sensor for Tactile Sensing in an Electronic Skin", Journal of Sensors, vol. 2016, Article ID 1736169, 7 pages, 2016. https://doi.org/10.1155/2016/1736169
Integration of a Thin Film PDMS-Based Capacitive Sensor for Tactile Sensing in an Electronic Skin
We present a capacitive force sensor based on a polydimethylsiloxane (PDMS) film integrated into a printed circuit board (PCB) on a flexible substrate whose layout is defined by inkjet printing. The influence of the dielectric thickness on the sensor behavior is presented. The thinner PDMS film of about 45 μm shows a sensitivity of up to 3 pF/N but poorer dynamic response. The dielectrics with thicknesses above 200 μm show a significantly reduced sensitivity. The best compromise between sensitivity and dynamic response is found for PDMS film of about 100 μm, showing about 1.1 pF/N and less than 15 s of recovery time. This film is integrated into a flexible PCBS including a microcontroller capable of evaluating the sensor. Interconnects of the circuit are defined by silver nanoparticles deposited by inkjet printing. The working principle of the circuit is demonstrated, proving that this simple approach can be used for artificial skin applications.
Over the last decades, there has been an increasing interest in the development of tactile sensing electronic devices able to provide “sense of touch” [1, 2]. In humans, the skin is the physical frontier between our environment and ourselves and helps us to interact in a successful way with the outer world. Apart from being a protective layer, our skin helps us to collect information of our surrounding environment and to perform essential tasks, such as motion control or grasping objects . To do that, human skin is composed of a large number of different detectors embedded in our skin at different levels and with variable densities. Those detectors are in charge of detecting different modalities: force, pressure, strain, light, and temperature. The collected information is converted into electrical signals that are processed by the central or peripheral nervous system in a more complex way. In fact, the human skin acts as an interface with the outside environment .
Printed Electronics (PE) makes use of traditional printing techniques, that is, screen-printing, gravure, inkjet printing, and so forth, to fabricate electronic circuitry. The recent advances in materials and fabrication techniques in PE are leading to a complete new generation of electronic devices with remarkable new features in traditional electronics, like flexibility, lightness, ultra-cost-effectiveness, and biodegradability. These properties are mandatory for artificial skin due to the mechanical requirements, weight restrictions, and the need for the device to be conformal with the shape of the object to be attached. Moreover, printing has the capability of manufacturing large products, up to several tens of meters wide. Sensor modules capable of performing tactile sensing have been already developed. Tactile skin devices should include measurements of strain, shear forces, pressure, and vibration [5–8].
In this framework, capacitive sensors are especially interesting and they have been employed to measure normal forces, shear forces, and strain [6, 9, 10]. They can be fabricated with small dimensions, providing a high spatial resolution. A combination of multiple sensors can be employed to detect forces of different types in all directions . Several groups have developed tactile sensor matrices or arrays [12, 13] and even some research groups made the attempt to completely cover a humanoid with artificial skin [14, 15]. In literature, several examples of the integration of an electronic skin for humanoids can be found [4, 16, 17].
In this work, we present a study of a simple but reliable capacitive sensor based on the elastomer polydimethylsiloxane (PDMS) film and its integration into a flexible printed circuit board (PCB) manufactured by inkjet printing. The mechanical properties of PDMS films have been already studied [18–21]. Thanks to its mechanical characteristics and its relative ease of manufacturing, several authors have used PDMS as the core material of force sensors. Mannsfeld et al. developed flexible capacitive pressure sensors based on microstructured thin PDMS films. They are capable of tuning the pressure sensitivity by using different microstructured patterns, such as lines and pyramids . Lipomi et al. introduced skin-like capacitive pressure and strain sensors where the silicone elastomer Ecoflex is placed between transparent elastic films of carbon nanotube (CNT) and PDMS, acting as electrodes . Lei et al. have shown a flexible capacitive pressure sensor based on PDMS developed for plantar pressure measurement in biomechanical applications . The designed sensor is capable of detecting up to 945 kPa and consists of four layers: lower layer, dielectric layer, upper layer, and bump layer. A work from Woo et al. presented a capacitive force sensor array based on a micro-patterned film of a conductive CNT-doped PDMS produced by a combination of soft-lithographic replication and contact printing . Flexible capacitive tactile sensors with microstructured PDMS as dielectric material and utilizing spray deposited CNT thin films as transparent conductors on polyimide substrates have been reported . The sensor can detect forces below 10 mN and a variation in capacitance of up to 20% for 1 N of applied force can be achieved with good long-term reliability. There are further studies in literature where a mixture of PDMS and CNT is used as resistive force sensor [26–28] but the capacitive approach is desirable for PCB design due to its high speed response and long-lasting reliability .
In the approach presented here, a capacitive sensor is characterized and integrated together with a microcontroller and other devices on a flexible substrate where interconnects are defined by inkjet printing of silver nanoparticles. The force sensor is a parallel plate capacitor whose dielectric is a PDMS film. The performances of different PDMS thicknesses have been compared with the aim of finding the most suitable one. This work demonstrates the feasibility of an unstructured PDMS film as a capacitive sensor integrated on a flexible PCB, bringing closer the development of artificial skin solutions.
2. Materials and Methods
The flexible substrate was Kapton with copper laminated onto the top surface (Pyralux® from DuPont, USA) that was used as one of the electrodes of our device. The other electrode was made of electrically conductive ink (DGP 40LT-15C from ANP Co., USA) with about 30–35% of silver nanoparticles and triethylene glycol monoethyl ether (TMGE) as solvent. The dielectric spacer used was the polydimethylsiloxane (PDMS) which consists of two components base and curing agent (Sylgard 184, Dow Corning).
2.2. Fabrication Process
The PDMS films were prepared by mixing the base and the curing agent in a weight ratio of 10 : 1, respectively. A mechanical stirring for the mixture was applied for 10 min. Then, the mixture is desiccated for 30 min to remove entrapped air bubbles resulting from stirring. The viscous PDMS mixture was then directly deposited onto the copper face of Kapton and spin-coated to reach the desired thickness of PDMS and get a uniform thin film at the same time. Spin coating at 10 rps for 30 s and 25 rps for 60 s resulted in a layer thickness of about 100 μm and 45 μm, respectively. Thicker films were composed of multiple spin-coated layers. Then, the film was desiccated again for 10 min to remove any enclosed air bubbles. Afterwards the PDMS is cured by placing the sample on a hotplate at 100°C for 60 min. The second electrode was inkjet-printed on the top layer of PDMS with a DMP-2831™ Dimatix printer (Fujifilm Dimatix Inc., Santa Clara, USA). The substrate temperature was fixed at 60°C during printing. The top electrode consisted of two consecutive printed layers. A drop space of 40 μm was settled in the printer for 80 μm landed diameter drops followed by a drying step at 80°C for 10 min.
After the drying of the silver layer at 80°C for 10 min, a photonic sintering (Sinteron 2010 from Xenon, USA) was conducted with a voltage of 2.5 kV and 15 pulses of 500 μs to ensure a good resistivity of the printed patterns. Finally, two wires were glued to the electrodes using silver-filled epoxy EPO-TEK® H20E (Epoxy Technology, Inc., Billerica, USA) and the device was dried at 60°C for 60 min.
The thicknesses of the PDMS films and silver electrodes were measured with a Dektak XT™ Stimulus Surface Profiling System (Bruker Corporation, Coventry, UK). Sheet resistance measurements were conducted on the printed electrode with a self-made linear four-point probe in combination with a Keithley ACS 2600 (Germering, Germany). A correction factor of 0.651 was calculated and applied to remove the effect of limited boundaries according to Smits .
The characterization of the force was performed as in . A voice coil actuator VM2836-180 from Geeplus (Beckenham, UK) was used to generate the normal force . By applying a current to the coil inside the actuator, a magnetic field was induced and the movable coil was displaced with respect to the permanent magnet. The coil of the actuator was attached to a metallic bar of mm diameter, which transfers the movement mechanically to the tactile sensor. A piezoresistive PK 88870 force sensor (FSG Series from Honeywell, Offenbach, Germany) was used to obtain feedback control on . The driving current was supplied to the actuator through a Keithley 2602 SourceMeter (Germering, Germany). The capacitance and series resistance of the fabricated sensors were continuously monitored using an Agilent E4980A Precision LCR Meter (Böblingen, Germany) at 100 kHz. The entire setup was controlled and data were recorded using the software LabVIEW (National Instruments Corporation, Texas, USA).
3. Results and Discussion
3.1. Physical Characterization
The structure with the shape presented in Figure 1(a) was printed on top of the dry PDMS, resulting in the sensor shown in Figure 1(b). The printed structures were designed with contacts of (3 mm × 3 mm) and (1 mm × 1 mm), where the distance between contacts was 1 cm with 1 mm width. Figure 1(c) illustrates the layers that composed this sensor.
After performing the photonic sintering process, the sheet resistance of the printed electrode was measured to be about Ω/□. An optical microscope image of the printed layer on top of the PDMS is depicted in Figure 1(d). The thickness of the printed silver on the PDMS film is shown in Figure 2. The typical coffee ring effect of printed layers can also be seen in the same figure. Surface profilometer measurements revealed the thickness of the printed silver layer on PDMS to be about nm. This is about one order of magnitude higher than silver layers on other substrates printed with the same drop spacing and drop waveform [31, 32]. This huge difference in height cannot be explained with a reduced packing density of the silver nanoparticles. The only other material in direct contact with the PDMS is the solvent of the ink. The used ink possesses around 95% (vol) of TGME that leads to a wet ink layer of approximately 6-7 μm after printing , which is close to the thicknesses we measured. We can exclude the possibility of entrapped solvent in the layer after drying by visual inspection of the silver-colored layer (Figures 1(b) and 1(c)). Thus, we could assume that the increased height of the printed silver tracks on PDMS is related to a swelling of the PDMS after solvent absorption. Among others, Lee et al. investigated the effect of many solvents on swelling using an immersed piece of PDMS  and found a swelling behavior for almost all tested solvents with a Hansen total solubility parameter close to PDMS. According to Dow Chemical  and the calculation method of Lee et al. this parameter is 10.1 for TGME. Other solvents having this parameter have a swelling ratio between 103% and 121%. The higher ratio leads to the swelling of the PDMS of about 4 μm already if the top 20 μm of PDMS is saturated with solvent. The swelling of the PDMS also explains the small increase in height next to the printed layers in Figure 2 between 0.5 and 0.6 mm.
3.2. Capacitive Sensors
Different PDMS films were prepared with different thickness values. Figure 3 illustrates the sensitivity () of the device defined as the change in capacitance in pF divided by the change in force in N:In all cases, we measured at 1 N force () and looked at after applying the force for 1 min.
As can be seen, the sensor sensitivity decreases exponentially with the increase in the PDMS thickness. This result is in agreement with previous reports in literature [18, 22]. Our objective here is to achieve a simple force sensor that can be easily integrated into a flexible PCB. Therefore, our sensor must be sensitive enough to be measured by a standard microcontroller and fast enough to do tracking of the applied force. At first glance, a thinner dielectric film leads to a higher sensitivity and, thus, a better performance. However, when we analyzed the dynamic response of the thinnest film (~45 μm), the time required to recover its initial capacitance value was much higher than the time required by the film of about 100 μm thickness. The thinnest layer requires more time to recover, while the 100 μm film needs less than 15 s. Furthermore, the 100 μm thick PDMS film used in this work has lower hysteresis in comparison to the one with a lower thickness. The reason behind is the fact that unstructured films, which are thinner than several hundred micrometers, are subject to significant viscoelastic creep. On the other hand, thicker unstructured PDMS films are nearly fully elastic under pressures lower than 100 kPa. As a result, thin PDMS films have higher relaxation times compared to thick films, which accounts for a higher hysteresis during device operation . For this reason, we selected the device with a PDMS film thickness of 100 μm, which presents the best compromise between nominal capacitance (~5 pF) and change under applied force (>20%).
Figure 4 illustrates the response of the selected sensor (~100 μm) when applying an increasing force of 50 mN every 30 s. This behavior can be approximated by a rational function with one zero and one pole; see (2). In particular, the parameters are = 5.81 pF, , and with . The response can also be approximated by linearization when we define the suitable force ranges. For instance, in 30–150 mN force range the sensitivity is about 3.7 fF/mN, while this sensitivity decreases to 0.7 fF/mN in 150–450 mN range and to 0.06 fF/mN at higher forces In order to observe the dynamic response of this sensor and its hysteresis and reproducibility, we performed different tests presented in Figure 5. Figure 5(a) illustrates the high reproducibility of the sensor as well as its fast time response to the force applied, although the recovery time is slightly longer than the response time.
As can be seen in Figure 5(b), the sensor goes back to its initial capacitance value if there is no force applied with an error less than 3% at the different force steps applied. If we compare this response with the one reported by Cagatay et al.  for a PDMS film of about 110 μm and pillar of about 30 μm, we observe similar capacitance values under no force. The sensitivity is about 10% lower in the sensor described here, but the fabrication procedure and the integration on a final system are much easier.
3.3. Sensor Integration
After showing the performance of the standalone sensor, we integrated it into a hybrid system of an inkjet-printed circuit board assembled with conventional surface mount components (Figure 6). The circuitry was printed with silver nanoparticle inkjet ink on a coated polyethylene terephthalate (PET) based substrate (Novele from Novacentrix, USA). From top left to bottom right, it contains a connector for programming the microcontroller (μC) and retrieving the measured values, four light emitting diodes (LEDs) with their corresponding serial resistor (R), and the sensor electrode. Above the sensor electrode, a piece of a 100 μm thick PDMS film was placed. Although we have demonstrated the possibility of direct printing the electrode on the PDMS, after pressing several times the silver layer on PDMS without any protection, this layer starts to show cracks. In order to avoid this issue and ensure longer durability of the system, we decided to employ another PET substrate with an inkjet-printed electrode on top of the PDMS film with the electrode facing down. These two electrodes touching the PDMS layer on each side form the capacitive sensor. All electrical connections were done with electrically conductive epoxy.
The microcontroller PIC24FJ64GA202 (Microchip) is equipped with a charge time measurement unit (CMTU), which was used to measure the capacitive sensor. We used a current () of 55 μA to charge the capacitor for 1.5 μs () with the charge . The resulting voltage at the electrodes was then converted to a digital value using the internal 12-bit analog-to-digital converter of the microcontroller with the reference voltage () at 3.25 V. This procedure allows us to calculate the measured capacitance following the equationThe measured force profile consists of a ramp with increasing force. Every 30 s the force was increased by 20% from 5 mN to 1000 mN. Force and average capacitance values were taken 25 s after each step to allow both values to stabilize. We measured the voltage 100 times and averaged it to increase the signal-to-noise ratio. Figure 7 shows a very small change of capacitance and a clear trend to higher capacitance at higher force. The relation between the capacitance and the force can be approximated by (2), where the parameter values are = 28.83 pF, , and at .
In comparison to direct capacitive measurements of the sensor, the microcontroller includes the parasitic capacitances of its input pins and the wires to the sensor. Based on the presented results above, this parasitic capacitance is in the order of 24 pF.
The relative change in the capacitance in this experiment is very small and touches the limits of the measurement capabilities of the microcontroller. One reason is the small sensor capacitance compared to the parasitic capacitance. This drawback could be overcome by using a strategy similar to the one presented by Toth and Meijer . As another possibility of improving the system performance, it is to enhance the sensor capacitance to raise sensitivity. It is suggested to increase the electrode area to the maximum size suitable for the application and/or use microstructured PDMS films that present higher sensitivities. The relative change in the sensor capacitance may be improved by using microstructured PDMS films that achieve a higher sensitivity by changing the average dielectric constant between the sensor electrodes.
In this work, a capacitive force sensor based on polydimethylsiloxane (PDMS) is presented. We have prepared different PDMS films by varying the film thickness. These films have been placed on a polyimide foil with copper layer, acting as bottom electrode, and a silver electrode has been printed on the other side of the PDMS, acting as top electrode. It has been observed that the thickness of the printed silver is 10 times higher than the one achieved in other substrates for the same ink with the same drop spacing and drop waveform. This increased height of the printed silver tracks on PDMS can be attributed to swelling of the PDMS after solvent absorption.
The PDMS film with about 45 μm thickness presents a sensitivity of about 3 pF/N or a change in capacitance of about 45%, whereas when the thickness increases the sensitivity is drastically reduced. Although thinner films result in higher sensitivities, the dynamic response is penalized and more time is required to recover the initial value. We found that the best compromise between the sensor sensitivity and its dynamic response is for thicknesses about 100 μm. For this kind of PDMS films, a nonlinear sensitivity of about 1.1 pF/N is achieved with a response time less than 15 s and no substantial hysteresis in its response.
The best candidate (~100 μm) has been characterized and integrated together with a microcontroller and other components on a flexible substrate, where interconnects are defined by inkjet printing of silver nanoparticles, proving the suitability of this technology to integrate those sensors in more complex printed circuits for artificial skin applications.
The authors declare that they have no competing interests.
This work was partially supported by the European Union through FP7-PEOPLE-2012-ITN 316832-OLIMPIA, FP7-PEOPLE-2013 607896-OrgBIO, and PITN-GA-2012-317488-CONTEST. This work was also partially funded by the TUM Graduate School.
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