Patent Description:
utilized graphene and Polydimethylsiloxane (PDMS) to make a hierarchically structured sensor<NUM>. Graphite was mixed with PDMS and cubic sodium chloride (NaCl) first. After washing out the NaCl, a porous composite film was attained. By using sandpaper as a mold, the surface morphology of this composite can also be microstructured. The developed sensor can be used to detect pressure based on a piezoresistive working principle, which is common to many tactile sensors and generally measures change in resistance when pressure is applied.

However, the porous microstructures attained were irregular in the fabrication method in<NUM>, and therefore the sensor is not adjustable to a desired performance for specific applications.

<CIT> describes a pressure sensor including a first electrode layer; a second electrode layer including multiple conductive microstructures extending toward the first electrode layer; and a dielectric layer between the first electrode layer and the second electrode layer.

<NPL>, describes a tactile sensor based on microstructured graphene arrays based on microstructured PDMS substrates, The microstructured graphene films, which serve as the sensitive layer of the resistive pressure sensor, are fabricated on the PDMS substrates by a layer-by-layer assembly process.

<NPL>, describes a force sensor with a surface morphology with spinosum microstructure of random distribution via the combination of an abrasive paper template and reduced graphene oxide.

<CIT> describes a condenser type pliable pressure sensor in which the upper and lower corresponding surface of substrate is spacedly distributed and has the micro-structure of array radial protrusion composition, the upper and lower corresponding surface of substrate is respectively equipped with the conductive layer for fitting closely with it and having same microstructure, and setting has the dielectric layer of pore structure between upper and lower conductive layers.

<CIT> describes a laminate comprising a polymer layer including a plurality of protrusions on one surface thereof and a conductive layer formed on one side of the polymer layer, wherein the surface of the protrusions is in the form of fine irregularities and the conductive layer is located on the surface of the protrusions. The surface of the protrusion of the laminate is in the form of irregularities.

<CIT> describes a flexible resistive array of pressure sensors and preparation method thereof, wherein flexible resistive array of pressure sensors includes surface encapsulation layer, electrode layer and functional layer, electrode layer includes the film metal line of several equidistant arrangements on substrate film and substrate film, and film metal line is connected with multi-channel gating device. The functional layer is the flexible resilient film that surface has raised micro-structure, and flexible resilient film is covered with the conductive metal wire of several equidistant arrangements, and conductive metal wire is connected with operational amplifier. The film metal line of electrode layer and the conductive metal wire of functional layer overlap assembly in a manner of square crossing.

Embodiments of the present seeks to address at least one of the above problems.

In accordance with a first aspect of the present invention, there is provided a composite structure for a pressure sensor as defined in claim <NUM>.

In accordance with a second aspect of the present invention, there is provided a pressure sensor comprising the composite structure as defined in claim <NUM>.

In accordance with a third aspect of the present invention, there is provided a method of fabricating a composite structure for a pressure sensor as defined in claim <NUM>.

In accordance with a fourth aspect of the present invention, there is provided a method of pressure sensing using the pressor sensor as defined in claim <NUM>.

Embodiments of the present invention provide a microstructured composite as a highly sensitive tactile sensor with attenuated viscosity in sensor performance. Embodiments of the present invention exploit the excellent deformability of a microstructured soft elastomer to attain high sensitivity and a wide sensitivity range. A stiff but flexible coating layer with both high Young's modulus (e.g. more than <NUM> times greater than that of the elastomeric microstructures) and flexibility, e.g. graphene, with a high Young's modulus up to <NUM> TPa, but also still flexible and stretchable, is designed on the surface of an elastomer according to example embodiments to reduce issues caused by viscoelastic effect. As a result, sensors according to example embodiments can achieve a high sensitivity of up to at least <NUM><NUM> Ω•kPa-<NUM>, with a wide detection range of <NUM> kPa in one example embodiment. Low hysteresis, temperature and strain rate independence are also observed. The sensors according to example embodiments are highly reliable and can maintain a consistent performance after a myriad of cycles, as well as after a long time. An analytical model is proposed to analyze the sensing mechanism of sensors according to example embodiments based on the change of contact resistance and quantum tunneling effect. The sensors according to example embodiments can be applied to detect small pressure (e.g. <NUM> Pa) and high-frequency signals (at least <NUM>).

Embodiments of the present invention use a more regular geometry of microstructures compared to a random geometry, with adjustable parameters, e.g. the size and density of micropyramids. Also, embodiments of the present invention use a structure based on the change of contact resistance, and utilize the high modulus (e.g. of at least <NUM> order of magnitude higher than the microstructures), and good flexibility of graphene (about <NUM> Tera Pascals) to achieve the viscosity reduced sensor performance.

Silicone elastomer and crosslinker were mixed at the weight ratio of <NUM>:<NUM>, followed by rigorous mixing at the speed of <NUM> rpms for <NUM> minutes. The mixture was spin-coated onto a non-stick layer treated (e,g, "Tosyl") silicon mold, which is patterned with micropyramid arrays with custom-designable sizes and spacing of each pyramid structure. For details of the patterning method used in example embodiments, reference is made to <NUM>. The sample was then degassed in a desiccator for <NUM> minutes to remove air bubbles generated during mixing. Polyethylene terephthalate (PET) was selected as the substrate and was treated with O<NUM> plasma to render the surface hydrophilic for better adhesion with PDMS. After degassing, the plasma treated substrate was pressed on top of the PDMS mixture on the mold, and cured at <NUM> for at least <NUM> hours. Finally, the mold was peeled off and the microstructured PDMS films remained on the substrate for further testing.

<FIG> shows a schematic illustration of the process to prepare Graphene/Graphene oxide layers on nanostructured PDMS film, according to an example embodiment.

Specifically, <FIG> provides a schematic depiction for sample preparation according to an example embodiment. Graphene oxide (GO) can be easily dispersed in water (e.g. <NUM>/ml) by ultrasonication for <NUM> hour, indicated at numeral <NUM>, and the quality of the dispersion can be well-maintained for a long time without aggregation and precipitation. The GO was then transferred, indicated at numeral <NUM>, onto the O<NUM> plasma treated elastomer, here PET, substrate <NUM> with microstructured PDMS <NUM>, followed by blading, indicated at numeral <NUM>, for more even deposition and to remove excess GO, which contributed to a uniform GO layer <NUM>.

The nanographene (Gr) powders were firstly dispersed in N-Methyl-<NUM>-pyrrolidone (NMP) solution (<NUM>/ml), followed by ultrasonication of <NUM> hours, indicated at numeral <NUM>. The choice of a concentration of <NUM>/ml according to preferred example embodiments will be described below. A one-hour sedimentation process, indicated at numeral <NUM>, was used after the ultrasonication, which allowed unevenly dispersed Gr to gravitate from the top layer, while the finely dispersed supernatant Gr nanoflakes were drop casted, indicated at numeral <NUM>, onto the GO layer <NUM> and dried in an <NUM> oven for <NUM> minutes to form a uniform flexible conductive Gr coating <NUM>. <FIG> shows an atomic force microscopy (AFM) image of the edge of the Gr coating <NUM> and the intermediate GO layer <NUM>, indicating a total height of about <NUM> according to an example embodiment.

It is noted that when using NMP as in the method described above according to an example embodiment, the substrate of the sensor preferably does not react with NMP, e.g. PET film was used in the embodiments described herein. NMP can be replaced in other embodiments to extend the range of substrates.

<FIG> shows SEM images of as-prepared Gr-GO on polymer sample (a) - (c) using the blading method described above for GO and supernatant Gr, (d) using bottom Gr, (e) without the presence of GO layer, (f) a thin layer of GO was coated by the blading method described above, (g) a thick layer of GO and buckles were formed by drop casting of GO.

Specifically, <FIG> show the SEM images of the microstructured composite. There are some key factors that can affect the quality of the composite structure according to example embodiments. Firstly, after sedimentation, if bottom Gr was used for drop casting, the coating was found to be uneven and so dense that it covers all the microstructures that are responsible for sensitivity, and can be easily delaminated when pressure is applied, as can be seen from the SEM image in <FIG>. Secondly, if no GO layer is present, the Gr nanoflakes tend to aggregate and the deposition will be non-uniform, as can be seen in the SEM image in <FIG>. It is believed that the thin GO layer, serving as an interface layer between the polymer and Gr, provides better affinity to Gr mainly due to π-π interaction and contributes to the formation of a Gr layer with better uniformity, according to preferred embodiments. Furthermore, the thickness of the GO layer is preferably controlled. <FIG> show a GO on PDMS sample prepared by blading and drop-casting, respectively. As can be seen from the SEM images in <FIG>, the GO layer coated by blading according to preferred embodiments was sufficiently thin to maintain the surface morphology of microstructured PDMS, while the drop-casted GO significantly changed the original microstructure, leaving air gaps at the side edges of the micropyramids and also buckles. Therefore, in order to form high-quality Gr-GO layers on PDMS microstructures, it is preferred to use supernatant Gr and blading coated GO.

In embodiments which allow GO to interact with PDMS only through Van Der Waals force, the film may be detached if strong shear, bending or adhesive forces are presented. Several methods can be implemented according to preferred embodiments to improve the adhesion between GO and PDMS. One method can be sputtering of thin-layer copper on PDMS, followed by GO deposition and annealing at <NUM> for <NUM> hours, which contributed to the formation of chemical bonds between copper and GO to enhance the adhesion strength. Another method focuses on the electrostatic interaction. As GO is negatively charged, a surface treatment can be conducted on the PDMS surface to render it positively charged. This strategy can generate a strong electrostatic force between GO and PDMS to greatly enhance the adhesion.

The present invention is not limited to the materials used in the example embodiments described above.

In various embodiments, the present invention can, for example, be also applied to other low-dimensional electronically active material systems for the flexible conductive coating such as, but not limited to, coatings made from other carbon allotropes such as graphyne and other added 2D materials such as borophene, tungsten selenide, silicene, etc. These active 2D materials can be dispersed in suitable dispersants and coated on the surface of elastomeric microstructures using the same method described above with reference to <FIG>. The conductive path formed on the elastomer surface can lead to the change of resistance when the pressure is applied.

Other elastomeric materials can include, but are not limited to, other polymers e.g. (styrene-ethylene-butylene-styrene) (SBS), silicones and polyurethanes, which provide a wide range of selective mechanical performances for various requirements.

Elastomers usually exhibit good deformability because of their low elastic moduli, which benefits in designing pressure sensitive elements. On the other hand, their performances are strongly affected by viscoelastic effects, e.g. hysteresis. However, the sensor according to example embodiments can advantageously utilize the properties of an outer graphene layer to reduce prohibitive viscoelastic effects and instead exhibit low hysteresis, weak temperature dependence, and weak strain-rate dependence without sacrificing sensing performances (e.g. high sensitivity, wide sensitive range). Based on the contact resistance change as the principal sensing mechanism, the electrical performances of the sensors according to example embodiments highly depend on the pressure response of the outer layer. Thus, the issues associated with viscosity can be compensated by the graphene coating according to example embodiments, which exhibit more elastic properties. The characterization of sensors according to example embodiments demonstrated the reduced viscoelastic effects, and are described below.

In the example embodiment characterized below, each micropyramid has a basal size of <NUM> and a height of <NUM>. The spacing of two pyramids is <NUM>. It is noted that the present invention is not limited to those sizes.

The thickness of graphene layer is <NUM> and the thickness of graphene oxide layer is <NUM>. It is noted that the present invention is not limited to those thicknesses and materials.

For characterization, the composite according to example embodiments was assembled with designed interdigital electrodes <NUM>, <NUM> formed on a substrate (not shown) surface opposing the coated microstructures <NUM> as the graphene sensor <NUM> according to an example embodiment, see <FIG>.

Specifically, the microstructure/sensor arrays <NUM> were center-aligned on the interdigital electrodes <NUM>, <NUM> (see <FIG>) with the coated pyramid tips <NUM> (compare <FIG>), in this embodiment, facing down to contact with the electrodes <NUM>, <NUM>. A commercial biocompatible tape can be used to seal the sensor arrays on the electrodes <NUM>, <NUM>.

In one example embodiment, the interdigital electrodes <NUM>, <NUM> were fabricated using a standard lithography process. A photoresist was coated on the substrate and exposed to the UV light under a photomask. The photomask has the interdigital electrodes patterns, which were transferred to the photoresist after developing it. Then titanium (Ti) and gold (Au) were sputtered onto the photoresist. After the lift-off, the excess photoresist and metals were washed out with the interdigital-patterned metals left on the substrate as the electrodes.

The designed interdigital electrodes <NUM>, <NUM> cover a slightly larger area than the sensor itself for a more robust performance according to an example embodiment, which will be discussed in the theoretical analysis section below, as schematically shown in <FIG>. When the compressive pressure (<NUM> kPa) was applied on the sensor using a custom-designed linear stage system with a strain rate of <NUM>/s, the resistance changed from the order of <NUM><NUM> Ω to the order of <NUM><NUM> Ω.

<FIG> Shows a graph of resistance versus pressure of graphene sensors according to example embodiments: <FIG> Forward and backward response. The inset graph shows the relationship of sensitivity versus pressure. <FIG> Pressure responses of graphene sensors according to various embodiments. <FIG> The effect of Gr concentrations on tunable pressure responses according to example embodiments.

Specifically, <FIG> shows the resistance change corresponding to the applied pressure according to an example embodiment. Both loading and unloading results are indicated. Only a small electrical hysteresis was observed compared to previously reported piezoresistive sensors, showing great potential for accurate sensing applications. This reduced hysteresis is attributed to the high modulus of the graphene coating according to example embodiments, which advantageously imparts more elastic properties on the sensors.

The inset graph in <FIG> shows the relationship between pressure and sensitivity. The definition of sensitivity is <MAT>, referring to the resistance change within a very small change of the pressure. The sensitivity of the graphene sensor according to example embodiments can go up to at least <NUM><NUM> Ω•kPa-<NUM> when the applied pressure is small, indicating a good ability to detect the minute force. When the pressure increases, the sensitivity will decrease as expected.

As the pressure-sensitivity curve can be attained from the differentiate of the pressure-resistance curve through the definition of sensitivity, the smooth and consistent relationship of sensitivity versus pressure shows the stability of sensor performance according to example embodiments. <FIG> shows the electrical pressure responses of multiple graphene sensors according to example embodiments, indicated as samples <NUM> to <NUM>. The comparable results indicate the reliability of the fabrication methods and resulting sensors according to example embodiments. Furthermore, the Gr concentration used for coating was found to be a key factor that affects the pressure response of the sensor. According to example embodiments, sensor performance can be adjusted by tuning the concentration of Gr. As shown in <FIG>, "C10T1" (meaning <NUM>/ml in concentration and one single coating) presents the largest sensitivity range compared with "C5T1" and "C2T1" (meaning <NUM>/ml and <NUM>/ml respectively, in concentration and single coating), according to various example embodiments.

<FIG> shows a graph illustrating the strain rate independence of graphene sensors according to example embodiments. The pressure responses are identical at different strain rates. Fig. (b shows a graph illustrating the temperature independence of graphene sensors according to example embodiments. The pressure response shows an insignificant change when the temperature increases from the room temperature to <NUM>.

For viscoelastic materials such as PDMS, the relationship between the load and response is a function of frequency because its viscous effect obeys Newton's law. When the pressure is applied at different strain rates, the corresponding response of PDMS is expected to be different. However, due to the flexibility and high modulus, the graphene layer coated at the outside according to example embodiments can make itself easily deform with the inner PDMS while mainly exhibiting elastic properties, which refers to the obedience of Hooke's law. According to example embodiments, the contact area between the electrodes and graphene layer is not visibly affected by the frequency, leading to a strain-rate independent resistance change of the sensor upon applied loads. <FIG> illustrates that the electrical responses of the graphene sensors according to example embodiments are almost identical at different strain rates. The result shows that sensors according to example embodiments can work reliably with loads applied at various frequencies, which also indicates the sensors according to example embodiments have great potential to detect vibrations. This will be described below in more detail.

For the effect of temperature, graphene has a much smaller thermal expansion coefficient compared with PDMS when the temperature increases, which can advantageously reduce the shift of sensor response induced by the geometric expansion of the sensor structure during temperature change. On the other hand, the temperature coefficient of resistivity (TCR) of graphene is extremely small, which indicates the resistivity of graphene is dominated by impurities and changes slowly with temperature. These two reasons contribute to the minimal temperature dependence of the graphene sensors according to example embodiments (see <FIG>), compared with previously reported work. The performances of existing sensors are highly dependent on temperature, whereas the sensors according to example embodiments can advantageously work more reliably regardless of the temperature change, which indicates stronger robustness at different working conditions.

<FIG> Shows graphs illustrating the reliability of graphene sensors according to example embodiments when subjected to cyclic compressions and long period of time: <FIG> The pressure response from the <NUM>st cycle to the <NUM>,<NUM>,<NUM>th cycle. <FIG> The loading and unloading responses after <NUM>,<NUM>,<NUM> cycles, showing that the hysteresis still remains at only a low extent. <FIG> Continuous measurement of sensor performance over <NUM> cycles. <FIG> The loading and unloading responses of a graphene sensor according to an example embodiment after <NUM> weeks from fabrication, showing the good reliability of the sensors according to example embodiments over days.

Specifically, to characterize the sensor reliability during cyclic loads, the graphene sensors according to example embodiments were subjected to a cyclic pressure of <NUM> kPa for <NUM>,<NUM>,<NUM> times. <FIG> presents the corresponding sensor performances from the 1st cycle to the <NUM>,<NUM>,000th cycle. Both sensitivity and sensitive range remained stable and consistent after <NUM>,<NUM>,<NUM> cycles. The mostly comparable sensor responses before and after <NUM>,<NUM>,<NUM> times of compression indicate the good reliability and compressibility of the graphene sensor. The slight shift of resistance observed especially during the first <NUM> cycles may be induced by a more compact contact between various graphene flakes of the coating layer. This circumstance also appears in <FIG> and the quantum tunneling phenomenon arisen by these uncompact graphene flakes will be discussed below. The loading and unloading responses of a graphene sensor according to an example embodiment were plotted at the <NUM>,<NUM>,<NUM>th compression in <FIG>. The low hysteresis is still maintained after a myriad of cycles, showing a reliable performance and high accuracy of the sensors according to example embodiments. In addition, the good adhesion between Gr-GO and PDMS according to example embodiments was also revealed and the outer layer would not be degraded or damaged after the myriad of cycles, by virtue of its unique flexibility. Furthermore, <FIG> displays the continuous measurement results of sensor responses over the first <NUM> cycles of compression. During the loading with constant amplitude (<NUM> kPa), the maximum conductance of the sensor slightly increased first, due to a more compact stack of graphene flakes. Later, it remained unvaried and stable over cycles. A good sensor reliability is illustrated from the characterization results.

In previous work studying PEDOT:PSS coated microstructured sensors, the sensor performance would degrade with time and became less sensitive. The reason for the degradation is because the PSS part will react with water and lead to the degeneracy. However, graphene is highly inert and can advantageously work as a corrosion barrier against water and oxygen diffusion. In this case, the sensor coated with Gr-GO according to example embodiments can maintain its sensing ability even after a long period of time. <FIG> illustrates the pressure responses (both loading and unloading) of a graphene sensor according to an example embodiment after <NUM> weeks from fabrication. Good sensitivity, wide sensitive range and low hysteresis are still exhibited without degradation. This property is significant for the use of sensors according to example embodiment in applications like wearable devices and health monitoring system.

<FIG> shows schematic drawings illustrating simulation of the equivalent surface resistance of graphene sensors according to example embodiments, with <FIG> "electrodes in sensor" design, and <FIG> "sensor in electrodes" design. <FIG> shows a schematic of the equivalent circuits of graphene sensor according to example embodiments.

The reason for utilizing interdigital electrodes according to preferred example embodiments is to increase the contact area between sensor and electrodes, and to reduce the effect of possible unevenly distributed coating defects. When the current passes through the surface of the micropyramids according to some example embodiments, each structure with Gr-GO coating can be regarded as one resistor. The equivalent circuit of an array of micropyramids is lots of resistors in series and in parallel connection. The software TINA was utilized for modeling and analyzing the resistance of this circuit (including the design of electrodes) to attain its equivalent resistance. When simulating the electrodes, several parameters were taken into account e.g. the size, length, displacement, and position of the electrodes. The size of the electrodes was found to be important. Different designs of sizes can lead to different characterization results of sensor performance, according to various example embodiments.

For the design of "electrodes in sensor" which refers to the case that the sensor has a larger surface area than the electrodes, in addition to the length and displacement of the electrodes, other factors like the position of the electrodes, and dimension of the sensor, will also effect the resistance of the sensor (see <FIG>). In <FIG>, the lager surface area of the sensor is illustrated by the length of electrodes e.g. <NUM> within the sensor resistance network <NUM> being shorter than the corresponding length <NUM> of the sensor resistance network <NUM>.

However, for the design of "sensor in electrodes" which refers to the case that electrodes have a larger surface area than sensor, only the displacement and length of electrodes was found to affect the resistance within expectation (see <FIG>). In <FIG>, the larger surface area of the electrodes is illustrated by the length of electrodes e.g. <NUM> within the sensor resistance network <NUM> being the same as or larger than the length <NUM> of the sensor resistance network <NUM>. The investigation result can make the circuit more robust during the sensor characterization. Hence, the latter design was selected for preferred embodiments. The resistance increases with the increased displacement of two electrodes, and it reduces with the increased length of electrodes. This phenomenon can further simplify the equivalent circuits to a "m × n" resistance network (see <FIG>), where m is proportional to the length of the electrodes and n is proportional to the displacement.

<FIG> shows I-V curves of a graphene sensor according to an example embodiment under different applied loads (<NUM> kPa, <NUM> kPa, and <NUM> kPa, respectively). The non-linear relationship indicates the quantum tunneling effect in the sensor according to the example embodiment.

With reference to <FIG>, when the Gr-GO/PDMS composite is assembled with electrodes to form the sensor <NUM> according to an example embodiment, one pair of interdigital electrodes <NUM>, <NUM> is used for the testing. The interdigital electrodes <NUM>, <NUM> consist of two interlocking comb-shaped arrays of metal, whereby the electrodes <NUM>, <NUM> are co-located adjacent to each other on the same surface of the substrate. The current will flow from one electrode <NUM>, passing through the Gr-GO coating on the surface of the microstructures, e.g. micropyramids, and then into the other electrode <NUM>. The total resistance of the sensor according to example embodiments is contributed by three parts: electrodes resistance (Re), contact resistance (Rc), and surface resistance of Gr layer (Rs). Re does not change with pressure. Rc significantly changes with pressure mainly due to the change of contact area and also due to some quantum tunneling effects from stacked graphene flakes. Rs slightly changes with pressure due to the change of surface area during compression, but this change is minuscule compared with the change of Rc.

The simplified circuit is shown in <FIG>. Rs is regarded as the aggregation of the resistor network with approximated constant resistance. Rc is the aggregation of microstructures, here micropyramids which are contacted with electrodes and having a pressure-induced resistance change. Each micropyramid is regarded to have the same resistance, as well as the same resistance change during loading. The number k is related to the area of electrodes, and also the density of micropyramids. <FIG> illustrate the I-V curves of a graphene sensor according to an example embodiment under different applied loads (<NUM> kPa, <NUM> kPa, and <NUM> kPa, respectively). The resistance decreases with the increase of the applied voltage, indicating the quantum tunneling effect existing in the graphene sensors according to example embodiments. The tunneling effect comes from the nano-scale gaps between graphene flakes. Because the distance of each gap will be reduced with creased pressure the tunneling effect will get attenuated during the compression at higher pressure. This is revealed in <FIG>, through the reduced nonlinearity of I-V relationships observed when the pressure increases.

8a and 8b illustrate the continuous detection of small weights by sensors according to example embodiments. Specifically, as the graphene sensors according to example embodiments can sense the tactile pressure sensitively and stably, an experiment of continuous detection of small weights was carried out. The sensor with a dimension of <NUM> × <NUM> according to an example embodiment was fabricated to detect small weights of <NUM>, <NUM> and <NUM>. The minimum pressure corresponded to around <NUM> Pa. As shown in Fig. 8a, the sensor according to an example embodiment can continuously detect these small weights with good stability for a duration of around <NUM>. As shown in Fig. 8b, the sensor according to an example embodiment is able to output a consistent resistance change for the same small, indicating its good ability to sustainably sense ultra-small tactile signals. From previous studies, the touch receptors on human fingertips can sense pressure with a rough range of <NUM> Pa to <NUM> kPa. Compared with such a requirement, the sensors according to example embodiments have good potential to be utilized in electronic skin, exhibiting a sensing range from <NUM> Pa to <NUM> kPa in one example embodiment.

In addition to a wide sensing range, a high time resolution is also desired for a tactile sensor, which refers to the ability to distinguish signals with high frequencies, e.g. vibration. In nature, the protein fiber spun by spiders exhibits a unique combination of high tensile strength and good extensibility. The network structure using these spider silks contributes to the excellent vibration detection function of a spider web. For sensors according to example embodiments, graphene also has a very high modulus and owns certain flexibility simultaneously, similar with the spider web in terms of both structure and properties. Owing to these similarities, a fast time response is advantageously exhibited by graphene sensors according to example embodiments, providing for the ability to detect high frequencies. Thus, the sensors according to example embodiments are capable of recognizing a great time resolution to the tactile pressure, which can be applied to detect the vibration.

<FIG> shows a schematic representation of a setup for the detection of vibration using a graphene sensor according to an example embodiment. Acoustic wave was utilized to generate dynamic forces with high frequencies. <FIG> shows a graph illustrating the detection results of dynamic forces with frequencies of <NUM>, <NUM> and <NUM>. <FIG> shows the Fast Fourier Transform (FFT) of the respective detection results in <FIG> , showing the corresponding frequencies <NUM>-<NUM> that the sensor detected.

With reference to <FIG>, in order to provide the high-frequency signal in an experimental setup, a speaker <NUM> was utilized to generate the acoustic wave with custom-adjustable frequency. The acoustic wave was vertically applied on the surface of a sensor <NUM> according to an example embodiment to induce a dynamic force. Once the sensor <NUM> receives the dynamic force, it will be expeditiously compressed and released to correspondingly give a dynamic electrical response. As the graphene sensor <NUM> according to an example embodiments has a frequency-independent pressure response, the different frequencies will not affect the amplitude of sensor response. This property is beneficial for the detection of vibration and the accurate recognition of frequency without bringing in other factors. The sensor <NUM> according to an example embodiment was shown to be able to detect the vibration with a high frequency of at least <NUM>. <FIG> gives the detection results of the vibration with frequencies of <NUM>, <NUM> and <NUM>. By using the fast Fourier transform (FFT) algorithm to analyze the electrical response through the sensor output, the frequency of vibration can be recognized. <FIG> illustrate the FFT analysis results of these signals (<NUM>, <NUM> and <NUM>, respectively).

In the main embodiment, a composite structure for a pressure sensor is provided, the composite structure comprising an array of microstructures made from an elastomeric material; and a flexible conductive coating formed on the array of microstructures with a sufficiently thin thickness such that a surface morphology of the array of microstructures is substantially maintained for the coated array of the microstructures; wherein the conductive coating exhibits a Young's modulus that is higher than that of the elastomeric material.

The Young's modulus may be about one order of magnitude higher than that of the elastomeric material, or more.

The flexible conductive coating comprises a low dimensional electronically active material system. The low dimensional electronically active material system exhibits electron tunneling properties.

The low dimensional electronically active material system comprises a uniform layer.

The low dimensional electronically active material system may comprise 2D material structures. The 2D material structures may comprise nanoflakes.

The composite structure may further comprise a substrate for the array of microstructures.

The composite structure may further comprise an intermediate layer between the array of microstructures and the flexible conductive coating for improved uniformity of the flexible conductive coating.

In one embodiment, a pressure sensor comprising the composite structure of the above embodiment is provided.

The pressure sensor may exhibit a reduced hysteresis based on elastic properties of the composite structure compared to viscoelastic properties of the elastomeric material of the array of microstructures.

The pressure sensor may exhibit a substantially frequency independent pressure response.

The pressure sensor may exhibit a substantially temperature independent pressure response.

The pressure sensor may exhibit a substantially humidity independent pressure response.

The pressure sensor may further comprise electrodes disposed on the coated array of microstructures for measuring a resistance of an electric path comprising a portion of a surface of the coated array of microstructures. The electrodes may comprise two interdigital electrodes. The resistance may change as a result of compression of the coated array of microstructures under a pressure. The resistance may decrease with increasing pressure.

<FIG> shows a flowchart <NUM> illustrating a method of fabricating a composite structure for a pressure sensor, according to an example embodiment. At step <NUM>, an array of microstructures made from an elastomeric material is formed. At step <NUM>, a flexible conductive coating is formed on the array of microstructures such that a surface morphology of microstructures is substantially maintained for the coated array of the microstructures, wherein the conductive coating exhibits a Young's modulus that is higher than that of the elastomeric material.

Forming the flexible coating comprises drop casting a first material onto the array of microstructures.

The method may comprise blading a second material onto the array of microstructures prior to drop casting the first material.

The first material comprises a low dimensional electronically active material system.

The low dimensional electronically active material system exhibits electron tunneling properties.

The low dimensional electronically active material system may comprise a uniform layer.

The electronically active material system may comprise 2D material structures. The 2D material structures may comprise nanoflakes.

The method may further comprise disposing electrodes on the coated array of microstructures for measuring a resistance of an electric path comprising a portion of a surface of the coated array of microstructures.

In one embodiment, a method of pressure sensing using the pressor sensor of the above embodiment is provided.

Embodiments of the present invention can have one or more of the following features and associated benefits/advantages:.

Embodiments of the present invention can have the following applications, by way of example, not limitation:.

Aspects of the systems and methods described herein, such as the signal processing of the electrical signals, may be implemented as functionality programmed into any of a variety of circuitry, including programmable logic devices (PLDs), such as field programmable gate arrays (FPGAs), programmable array logic (PAL) devices, electrically programmable logic and memory devices and standard cell-based devices, as well as application specific integrated circuits (ASICs). Some other possibilities for implementing aspects of the system include: microcontrollers with memory (such as electronically erasable programmable read only memory (EEPROM)), embedded microprocessors, firmware, software, etc. Furthermore, aspects of the system may be embodied in microprocessors having software-based circuit emulation, discrete logic (sequential and combinatorial), custom devices, fuzzy (neural) logic, quantum devices, and hybrids of any of the above device types. Of course the underlying device technologies may be provided in a variety of component types, e.g., metal-oxide semiconductor field-effect transistor (MOSFET) technologies like complementary metal-oxide semiconductor (CMOS), bipolar technologies like emitter-coupled logic (ECL), polymer technologies (e.g., silicon-conjugated polymer and metal-conjugated polymer-metal structures), mixed analog and digital, etc..

The above description of illustrated embodiments of the systems and methods is not intended to be exhaustive or to limit the systems and methods to the precise forms disclosed. While specific embodiments of, and examples for, the systems components and methods are described herein for illustrative purposes, various equivalent modifications are possible within the scope of the systems, components and methods, as those skilled in the relevant art will recognize. The teachings of the systems and methods provided herein can be applied to other processing systems and methods, not only for the systems and methods described above.

The elements and acts of the various embodiments described above can be combined to provide further embodiments. These and other changes can be made to the systems and methods in light of the above detailed description.

In general, in the following claims, the terms used should not be construed to limit the systems and methods to the specific embodiments disclosed in the specification and the claims, but should be construed to include all processing systems that operate under the claims. Accordingly, the systems and methods are not limited by the disclosure, but instead the scope of the systems and methods is to be determined entirely by the claims.

Claim 1:
A composite structure (<NUM>) for a pressure sensor, the composite structure comprising
an array of microstructures (<NUM>) made from an elastomeric material; and
a flexible conductive coating formed on the array of microstructures with a sufficiently thin thickness such that a surface morphology of the array of microstructures is substantially maintained for the coated array of the microstructures;
wherein the conductive coating exhibits a Young's modulus that is higher than that of the elastomeric material; and
characterized in that the flexible conductive coating comprises a low dimensional electronically active material system, the low dimensional electronically active material system exhibiting electron tunneling properties.