In this paper, we present a protocol to selectively deposit organic materials on textiles, which allows for the direct integration of organic electronic devices with wearables. The fabricated devices can be fully integrated in textiles, respecting their mechanical appearance and enabling sensing capabilities.
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Ismailov, U., Ismailova, E., Takamatsu, S. A Simple and Scalable Fabrication Method for Organic Electronic Devices on Textiles. J. Vis. Exp. (121), e55439, doi:10.3791/55439 (2017).
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Today, wearable electronics devices combine a large variety of functional, stretchable, and flexible technologies. However, in many cases, these devices cannot be worn under everyday conditions. Therefore, textiles are commonly considered the best substrate to accommodate electronic devices in wearable use. In this paper, we describe how to selectively pattern organic electroactive materials on textiles from a solution in an easy and scalable manner. This versatile deposition technique enables the fabrication of wearable organic electronic devices on clothes.
The field of wearable electronics is a fast-growing market expected to be worth 50 billion euros in 2025, over three times the current market. The main challenge facing current wearable devices is that intrusive solid electronic attachments limit the usage of established devices in wearable systems. Using textiles that are already present in everyday life is a very attractive and straightforward approach to avoid this limitation. Due to its elastic capability, some parts of the clothing that we wear are naturally in tight contact with the skin. Many examples of smart clothes available on the market today are based on thin, plastic displays, keyboards, and light source devices embedded in textiles, linking electronics with humans in a fashionable way1. In sport practice, health monitoring relies on textile electrodes, which offer comfortable alternatives to commonly used adhesive electrodes and metal wristbands. Here, conductive fibers are directly integrated with stretchy fabrics to prevent skin irritation and other discomforts during extended wear. Additionally, textiles offer a number of opportunities to integrate curvature sensors to capture motion2, to integrate shear sensors for the development of functional robotic actuators3, and certainly to integrate biosensors through the detection of an analyte in sweat4.
Modern wearable technology relies on carbon-based semiconductor materials that deliver electronic devices with unique properties. The "soft" nature of organics offers better mechanical properties for interfacing with the human body compared to traditional solid-state electronics. This mechanical compatibility, paired with mechanically flexible substrates, enables the use of non-planar form factors in devices such as textiles. The use of organics is also relevant in life sciences due to their mixed electronic and ionic conductivity5. Besides, organic semiconducting and optoelectronic materials empower a large variety of functional devices with display, transistor, logic, and power capabilities6,7,8,9. The main difficulty in the fabrication of such organic devices is the controlled deposition of functional materials on the non-planar surfaces of textiles. Conventional microfabrication techniques are primarily limited by the incompatibility of the deposition process with the structural dimensionality of textile substrates.
Here, we describe a simple and scalable fabrication protocol that allows for the selective deposition of conducting polymers on structured textiles. The presented process enables the fabrication of wearable and conformal electronic devices. The approach is based on the patterning of the commercially available conducting polymer poly(3,4-ethylenedioxythiophene):poly(styrene sulfonate) (PEDOT:PSS) and an elastomeric stencil material polydimethylsiloxane (PDMS) on textile. This combination allows for the efficient confinement of the aqueous PEDOT:PSS solution, as well as for the retention of the soft and stretchable properties of textiles. This simple and reliable fabrication method paves the way for the fabrication of a variety of electronic devices directly on textiles in a cost-efficient and industrially scalable manner.
1. Patterning Conducting Polymers on Textile
- Fix a 10 cm x 10 cm textile sheet on a planar surface for easy handling during the process. For the textile, use a 100% interlock knit polyester fabric with a thickness of 300 µm and a knit direction stretch capability up to 50%.
- To make a mask containing the patterning design, use a 125 µm-thick polyimide film; an example of the pattern is illustrated in Figure 1.
- Use a laser cutter (e.g., Protolaser S, LPKF) to pattern the polyimide mask10; the pattern design of an electrode is illustrated in Figure 1.
- Coat the PDMS formulation (10:1 base to curing agent ratio) on top of the mask (polyimide film) using an automatic tape casting tool (K control print-coater, doctor blade) with a wet film thickness of 200 µm and at a 6 m/min coating speed. Use about 0.5 mL for a mask of 3 cm x 5 cm. Perform this process under the fume hood.
- Gently transfer the fabric to the PDMS-coated mask. Leave for 10 min, after which the PDMS should be fully absorbed in the textile structure.
- Cure the sample in an air-oven at 100 °C for 10 min.
- Prepare the conducting polymer:PEDOT:PSS dispersion (80 mL), ethylene glycol (20 mL), 4-dodecylbenzenesulfonic acid (40 µL), and 3-methacryloxypropyltrimethoxysilane (1 mL) in the fume hood.
- Brush-coat the PEDOT:PSS solution on the PDMS-free area of the textile until a homogenous penetration of the solution is obtained. Repeat this step to achieve a uniform pattern color. Apply about 1 mL/cm2.
- Cure the fabric at 110 °C for 1 h to dry the PEDOT:PSS solution. Reduce the temperature to 60 °C for textiles that are sensitive to high-temperature treatment, like nylon.
2. Organic Device Fabrication
NOTE: The protocol in Section 1 describes the selective deposition of conducting materials on textiles. The following sections will describe the additional steps needed to fabricate organic devices, like stretch sensors, OECT transistors, cutaneous electrodes, and capacitive sensors.
- To fabricate stretch sensors, shown in Figure 3a, pattern the electrode lines on the textile, as described in Section 1, steps 1.1-1.5.
NOTE: An example of the pattern design is shown in Figure 3a. The fabrication of such sensors does not require any additional steps.
- To fabricate the transistor design shown in Figure 3b, pattern the transistor arrays on a nylon woven ribbon following the steps described in Section 1. Slightly modify the PDMS annealing and PEDOT:PSS curing steps to avoid the thermal degradation of nylon by curing at 60 °C for a longer time.
- For the fabrication of cutaneous electrodes, shown in Figure 3c, deposit an ionic gel on the patterned PEDOT:PSS textiles.
- Prepare an ionic liquid gel mixture containing the ionic liquid, 1-ethyl-3-methylimidazolium-ethyl sulfate; the cross-linking agent, poly(ethylene glycol)diacrylate; and the photoinitiator, 2-hydroxy-2-methylpropiophenone at a (v/v) ratio of 0.6/0.35/0.05, respectively.
- Coat the PEDOT:PSS electrode with ionic liquid (20 µL/cm2) and add the ionic liquid gel mixture from step 2.3.1 (25 µL/cm2) by drop casting.
- Expose to UV light (365 nm) to initiate a crosslinking reaction for 10-15 min, until the gel solidifies. Perform this step in the fume hood Use a UV-protective cage during UV exposure.
- For capacitive sensor fabrication, use PEDOT:PSS textile electrodes insulated with an insulating material (Figure 3d).
- Insulate the keyboard-like PEDOT:PSS electrodes using the PDMS; the keyboard design can be seen in Figure 2b. Dispense the PDMS formulation on top of the fabric and remove the excess with a squeegee.
- Place the fabric in an oven at 100 °C for 10 min. Perform this step in the fume hood.
Traditional methods for applying colors or patterns to textiles rely on removable masking layers to allow the selective deposition of dyes. In Figure 1, we show the adaptation of such an approach to the patterning of PEDOT:PSS electrodes on textiles. As a masking layer, we used hydrophobic polydimethylsiloxane, which can restrain the non-controllable diffusion of the aqueous PEDOT:PSS solution. Moreover, the softness and stretchability of knitted and woven textiles can be preserved thanks to the elastic and mechanical properties of the PDMS.
In Figure 1, the process starts with the preparation of the patterning master from polyimide film (step 1). The design of the pattern outline is carved onto the film by a laser. Using a tape casting tool, the PDMS is applied on this master (step 2), and the textile is placed on top of it (step 3). The PDMS is then progressively diffused into the textile (step 4). To stop this transfer, a short thermal annealing process is required to cure the PDMS. The viscosity and thickness of the PDMS can be adjusted by using different amounts of the curing agent and coating parameters, respectively, to control the diffusion and to insure the faultless replication of the master design. Finally, the conducting solution is brush-painted on the unprotected textile and baked to dry (step 5). The polyimide master is then delaminated from the textile surface. The results of the fabrication flow are illustrated in Figure 1, on the right. In this case, successful patterning was placed on knitted polyester. The patterning resolution on such a textile is greater than 1 mm. However, lower resolution can also be obtained on tightly knit or woven textiles. Using this deposition technique, the estimated sheet resistance of the conducting textile is close to 230 Ω/sq.
Examples of functional electronic devices on knit and woven textiles are shown in Figure 3a and b, including successfully fabricated PEDOT:PSS electrodes on knit textiles. The natural horseshoe arrangement of the fibers in knit textiles provides adjustable stretchability to fabrics. This spring-like capability of knit structures can result in highly sensitive strain sensors11. A simple deformation in the textile structure is reflected by a change in the electrical resistivity due to the twisting of conductive fibers in the threads. Additionally, by taking advantage of the hygroscopic capacity of the textiles, the array of electrodes in Figure 3b was patterned on textiles to make planar transistors with rectangular channels and different gate widths, which can be used in wearable sweat sensing. Such a geometrical configuration is used in organic electrochemical transistors (OECT) for sensing which channel and gate are linked by a sample of an analyte12.
The presented patterning technique can be extended to fabricate complex organic electronic devices on textiles. As the PDMS stencil remains in the textile after the patterning process, additional layers can be patterned on PEDOT:PSS-coated conducting textiles. In Figure 2, we present the process in which an ionic liquid gel solution (Figure 2a) and the PDMS formulation (Figure 2b) were applied to functionalize or isolate the surface of a PEDOT:PSS electrode, respectively. Ionic gels are largely used in cutaneous electrodes. The incorporation of an ionic gel in conducting textiles was used to fabricate wearable textile electrodes for electrophysiological monitoring10 and is illustrated in Figure 3c. Capacitive sensors were made by insulating the textile electrode surface with PDMS. A change in the capacitance was detected when the electrode was touched. Such a touch-sensitive device was used to fabricate an organic electronic textile keyboard13, as shown in Figure 3d.
Figure 1. Process flow illustrating the patterning of conducting polymers onto textiles. Process flow illustrating the patterning of conducting polymers onto textiles. Step 1: mask preparation; step 2: PDMS deposition on the polyimide patterning mask defining the outline of the desired design; step 3: transfer of the masking layer by the placement of the textile on the PDMS-coated mask; step 4: transfer of the PDMS into the bulk of the textile, step 5: deposition of conducting polymer solution onto unprotected textile. The pictures on the right show the results of the key steps of the process flow. Please click here to view a larger version of this figure.
Figure 2. Two examples of fabrication organic devices. Two examples of fabrication organic devices. a) Ionic liquid gel coating on the PEDOT:PSS textile electrode for cutaneous sensing. b) Insulation layer deposition on the PEDOT:PSS textile electrode for touch sensors. Please click here to view a larger version of this figure.
Figure 3. Photographs of organic electronic textile devices. a) PEDOT:PSS electrodes for stretch sensing. b) Array of OECT transistors for wearable biosensing. c) Circular PEDOT:PSS electrode coated with an ionic liquid gel for cutaneous electrophysiology. d) Organic touch sensors for a wearable keyboard. Please click here to view a larger version of this figure.
The patterning of conducting materials is one of the first steps in the fabrication of functional electronic devices. This can become challenging, as the fabrication process needs to take into account the chemical and physical properties of such materials, and the process flow needs to consider the material cross-compatibility between the fabrication steps. In the microfabrication of organic electronic devices, these two aspects are even more significant due to the highly reactive nature of organics. Today, however, organic materials are highly attractive to wearable and flexible electronics for their electro-elastic properties14,15. The transfer of such technologies to textiles to obtain fully integrated electronic wearables is limited by their three-dimensional structures. Conventional techniques used in microfabrication are restricted to inkjet or screen printing of conducting inks only on thin substrates and textiles16,17,18. Traditional embroidery technique, where a single fiber is sewn into the textile, still lacks industrial production scalability.
The most critical aspect in the patterning of organic materials is deposition without disturbing the electrical properties. The patterning technique described in Figure 1 relies on the direct deposition of organics, with no need to meet specifications of the deposition technique or the tool. The organic materials are formulated to the best of their performances and can then be directly deposited on the chosen fabric structure. The utility of PDMS is key to pattern materials from solution onto textiles. The application of conducting materials from the low-viscosity solution, rather than using paste-like inks, enables a conformal and deep coating in textile structure. However, it limits the selective deposition and leads to the loss of the patterning resolution. We have overcome this limitation by creating a negative pattern from PDMS to restrain the non-controlled conducting solution penetration into the textile. The strategic choice of the PDMS is based on its visco-elastic properties, which maintain the textile stretchability and flexibility. The PDMS is also hydrophobic and allows the control of the spreading of the PEDOT:PSS water-based solution during the patterning. We observed that the conductive patterns fabricated using this protocol demonstrated good electrical conductivity and stability during mechanical deformations. This method allows the future customization of existing garments with smart components that have electronic capabilities. However, one of the critical and, in some cases, limiting points of the proposed approach is still organic material durability in wearable conditions. Some aspects, such as mechanical stress resistance and behavior after the washing and drying of organic conducting textiles, are still unknown.
The large majority of wearable electronics rely on stretchable devices, where spring-like structures are created to maintain the electrical connection during device deformation. Depending on the textile type, the fibers in knit fabrics are assembled in a horseshoe design, providing mechanical stretchability of the structure. Coating these textiles with conducting materials permits individual fibers to act as strain and motion sensors in smart clothing, as shown in Figure 3a. Moreover, more complex device geometries can easily be patterned, not only on knit, but also on woven fabrics. In Figure 3b, we present an array of OECTs with variable geometries. In conventional photolithography, the simultaneous fabrication of big and small features is almost impossible to achieve without requiring multiple steps. We demonstrate that our patterning technique is able to produce patterns with a resolution that varies from 0.5 mm to about a hundred times greater. Such transistors can be directly used in wearable sweat sensing with an adjustable time response and detection resolution19.
We have demonstrated that PDMS also enables the consecutive deposition of additional functional layers in a selective manner, as shown in Figure 2. Devices can then be integrated in textiles and become fully integrated on wearable systems. The process in Figure 2a shows the fabrication of a cutaneous textile electrode, where the contact between the electrode and the skin is enhanced with an ionic liquid gel. Wearable electrodes in cutaneous electrophysiology suffer from motion artifacts caused by the electrical contact degradation between the wearer and electrodes during recordings. The possibility to integrate ionic gels on textile electrodes opens an efficient communication channel with the human body, which is desired in wearable healthcare devices. An example of such a device can be seen in Figure 3c.
The consecutive deposition of other active materials can result in devices using a stack geometry, such as organic batteries, capacitors, solar cells, transistors, or sensors. Figure 2b shows the deposition route of insulating or dielectric materials. A wearable organic keyboard (Figure 3d) can be fabricated using this process, where the PDMS is used to create a dielectric layer on top of the electrode. Such a device is capable of capacitive variation sensing between the electrode and a finger, which can have potentially interesting applications in wearable computing and human-machine interfacing.
The authors have nothing to disclose.
The authors would like to acknowledge the BPI PIAVE AUTONOTEX grant for the financial support.
|SYLGARD 184, Silicone elastomer kit (Base and Curing agent)||Dow Corning||PDMS elastomer|
|The conducting polymer formulation|
|CleviosTM PH 1000 PEDOT:PSS||Heraeus||Conductive polymer|
|Ethylene glycol||Sigma-Aldrich||03750-250ML||Solvent (EG), CAS: 107-21-1|
|3-methacryloxypropyltrimethoxysilane||Sigma-Aldrich||M6514||Cros linker (GOPs), CAS: 2530-85-0|
|4-dodecylbenzenesulfonic acid||Sigma-Aldrich||44198||DBSA; CAS: 121-65-3|
|The ionic liquid gel|
|UV lamp DFE 2340||C.I.F/ ATHELEC||DP134||UV-365 nm|
|1-Ethyl-3-methylimidazolium ethyl sulfate||Sigma-Aldrich||51682-100G-F||Ionic Liquid (IL), CAS: 342573-75-5|
|Poly(ethylene glycol) diacrylate||Sigma-Aldrich||455008-100ML||Mn 700, CAS: 26570-48-9|
|2-Hydroxy-2-methylpropiophenon||Sigma-Aldrich||405655-50ML||Phot Initiator (PI), CAS: 7473-98-5|
|The textile fabric||VWR||Spec-Wipe 7 Wipers||100% interlock knit polyester fabric|
|The polyimide film||DuPont||HN100||Polyimide film with 125 µm thickness|
- Poupyrev, I., et al. Project Jacquard:Interactive Digital Textiles at Scale. Proceedings of the 2016 CHI Conference on Human Factors in Computing Systems - CHI '16. ACM Press. 4216-4227 (2016).
- Takamatsu, S., et al. Transparent conductive-polymer strain sensors for touch input sheets of flexible displays. J. Micromech. Microeng. 20, 075017 (2010).
- Patel, S., et al. A review of wearable sensors and systems with application in rehabilitation. J. Neuroeng. Rehabil. 9, 21 (2012).
- Bandodkar, A. J., et al. Epidermal tattoo potentiometric sodium sensors with wireless signal transduction for continuous non-invasive sweat monitoring. Biosens. Bioelectron. 54, 603-609 (2014).
- Owens, R. M., Malliaras, G. G. Organic Electronics at the Interface with Biology. MRS Bull. 35, (6), 449-456 (2010).
- Krebs, F. C., Biancardo, M., Winther-Jensen, B., Spanggard, H., Alstrup, J. Strategies for incorporation of polymer photovoltaics into garments and textiles. Sol. Energy Mater. Sol. Cells. 90, 1058-1067 (2006).
- Cherenack, K., Zysset, C., Kinkeldei, T., Münzenrieder, N., Tröster, G. Woven electronic fibers with sensing and display functions for smart textiles. Adv. Mater. 22, 5178-5182 (2010).
- Hamedi, M., Forchheimer, R., Inganäs, O. Towards woven logic from organic electronic fibres. Nat. Mater. 6, 357-362 (2007).
- Bao, L., Li, X. Towards Textile Energy Storage from Cotton T-Shirts. Adv. Mater. 24, 3246-3252 (2012).
- Takamatsu, S., et al. Direct patterning of organic conductors on knitted textiles for long-term electrocardiography. Sci. Rep. 5, 15003 (2015).
- Yamada, T., et al. A stretchable carbon nanotube strain sensor for human-motion detection. Nat. Nanotechnol. 6, 296-301 (2011).
- Shim, N. Y., et al. All-plastic electrochemical transistor for glucose sensing using a ferrocene mediator. Sensors. 9, 9896-9902 (2009).
- Takamatsu, S., et al. Wearable Keyboard Using Conducting Polymer Electrodes on Textiles. Adv. Mater. 28, 4485-4488 (2016).
- O'Connor, T. F., Rajan, K. M., Printz, A. D., Lipomi, D. J. Toward organic electronics with properties inspired by biological tissue. J. Mater. Chem. B. 3, 4947-4952 (2015).
- Choi, S., Lee, H., Ghaffari, R., Hyeon, T., Kim, D. Recent Advances in Flexible and Stretchable Bio-Electronic Devices Integrated with Nanomaterials. Adv. Mater. 28, 4203-4218 (2016).
- Zhang, Z., Qiu, J., Wang, S. Roll-to-roll printing of flexible thin-film organic thermoelectric devices. Manuf. Lett. 8, 6-10 (2016).
- Rim, Y. S., Bae, S. -H., Chen, H., De Marco, N., Yang, Y. Recent Progress in Materials and Devices toward Printable and Flexible Sensors. Adv. Mater. 28, 4415-4440 (2016).
- Matsuhisa, N., et al. Printable elastic conductors with a high conductivity for electronic textile applications. Nat. Commun. 6, 7461 (2015).
- Bernards, D. a, Malliaras, G. G. Steady-State and Transient Behavior of Organic Electrochemical Transistors. Adv. Funct. Mater. 17, (17), 3538-3544 (2007).