Adhesive com electrode patch self

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It can make you more involved and in control of your own health by monitoring effects of medi These are important vital signs to provide feedback on a pat Herein, we report an intrinsically conductive polymer dry electrode with excellent self-adhesiveness, stretchability, and conductivity.

It shows much lower skin-contact impedance and noise in static and dynamic measurement than the current dry electrodes and standard gel electrodes, enabling to acquire high-quality electrocardiogram ECG , electromyogram EMG and electroencephalogram EEG signals in various conditions such as dry and wet skin and during body movement.

Hence, this dry electrode can be used for long-term healthcare monitoring in complex daily conditions. We further investigated the capabilities of this electrode in a clinical setting and realized its ability to detect the arrhythmia features of atrial fibrillation accurately, and quantify muscle activity during deep tendon reflex testing and contraction against resistance. Human biopotentials such as electrocardiography ECG 1 , electromyography EMG 2 , and electroencephalography EEG 3 are significant for diagnosis and treatment of heart-, brain-, and muscle-related diseases 4.

These biopotentials can be transduced by electrically interfacing with the skin via epidermal electrodes. An efficient wearable electrode is crucial for accurately recording these biopotential signals, especially in the case of continuous monitoring of inconspicuous heart diseases and rehabilitation in daily life. Hence, significant effort has been devoted to the development of skin-friendly dry electrodes for biopotential measurements 6 , 7.

The dry electrodes in literature can be classified mainly into dry contact electrodes and dry capacitive noncontact electrodes 8. The dry capacitive electrodes give rise to motion artifacts quite sensitive to body movement, and thus are not suitable for biopotential monitoring. The dry contact electrodes mainly include thin metal films, conductive polymers composites, and intrinsically conductive polymers. Although thin metal films can have high conductivity, they are not stretchable and adhesive 9.

As a result, high noise can be observed on the biopotential signals, particularly during body movement. The research works on dry contact electrodes have been focused on soft conductive polymer composites and intrinsically conductive polymers due to their adaptation to rough and even deformed skin 9 , The conductive polymer composites consist of elastomers and conductive nanofillers like metals 11 , nanotubes 12 , nanowires 13 , and nanosheets The conductive nanofillers are the minority in the elastomer matrix, leading to a small effective contact area between the conductive nanofillers and human skin.

Mismatching between a dry electrode and human skin can occur during body movement, which can be improved if the dry electrodes are adhesive to human skin. Polymer composite patches with bio-inspired micro-pillar or sucker-like structures can be stretchable and adhesive 16 , Nevertheless, their adhesion to the skin is easily affected by secreted sweat or dirt on the skin, and clustering or contamination of the structures In addition, the suction induced adhesion of these structures can cause discomfort to patients.

There is also concern about the toxicity of the nanofillers 19 , Intrinsically conductive polymers can have high effective contact areas with human skin, biocompatibility, high electrical conductivity, and inherent mechanical flexibility 21 , 22 , Greco et al.

In addition, it is very difficult to handle ultrathin films. To obtain high-quality biopotential signals, a dry electrode should be conductive, biocompatible, stretchable, conformable, and self-adhesive to the skin. Nevertheless, intrinsically conductive polymers are neither stretchable nor adhesive to the skin. It possesses high conductivity and skin-compliant stretchability, with appreciated adhesion on dry and wet skin conditions, respectively.

This dry electrode can always give rise to high-quality epidermal biopotential signals, including ECG, EMG, and EEG, in various conditions such as dry and wet skin and during body movement. Moreover, this dry electrode can precisely identify the arrhythmia of a patient with atrial fibrillation and muscle activity in a clinical setting. The fabrication process of the self-adhesive dry electrode is illustrated in Fig.

D-sorbitol is further blended into the mixture to further increase its stretchability Moreover, D-sorbitol can enhance the adhesiveness of the polymer film on the substrates. The resulting blend film can be used as an adhesive electrode on the skin for epidermal biopotential detections such as electrocardiography ECG , electromyography EMG , and electroencephalography EEG. The SEM image indicates nanoscale grainy morphology Fig. Remarkably, the phase AFM image reveals the presence of two phases in the blend Fig.

S1 S5a , respectively. However, a further increase in D-sorbitol loading can cause remarkable moisture absorption, and make the PWS films volatile and hence susceptible to breaking. As shown in Fig. The resistance in the first three cycles remains almost the same.

In the repeated stretching and releasing cycles, the PWS electrodes exhibit stable conductivity Supplementary Movie 2. The conductance variation along the vertical direction can be even smaller S6a, b. The PWS films exhibit excellent adhesiveness on a glass substrate and skin. A PWS film of 2. Moreover, the PWS films can attach tightly on both smooth and hairy skin Fig. On the dry and wet skins with substantial wrinkles, the PWS films can adapt to the grooves of the wrinkles and adhere firmly Supplementary Fig.

S7 , Fig. The adhesion force of a pristine PWS film to the skin is 0. It increases slightly to 0. The increase in the adhesion force can be attributed to the change in film thickness by strain. The enhancement in the adhesion force of the stretched PWS film is attributed presumably to the better compliance of thinner film to skin They can tightly attach to a wrist that bends and twists vigorously and continuously Supplementary Movie 5 , Movie 6.

To evaluate the contact of PWS film to skin microscopically, a silicon rubber was used as the skin replica. The cross-section SEM image indicates that the PWS film is conformable to the uneven and curved surface of the skin replica in the sub-millimeter scale Fig. The 3D optical image taken with a confocal microscope displays clearly shows the replicated skin wrinkles on the PWS film detached from the skin replica Fig. The adhesion mechanism can be attributed to the physical adsorption of PWS to the skin and the mechanical force between them.

In addition, the soft PWS films can adapt well with the crevices of the skin, which not only increases the contact area between PWS and skin but also induces adhesive force between them. S11a, c. The further increase of D-sorbitol loading in the PWS film decreases its adhesiveness.

The adhesive force is 0. This force is attributed to the wet and slippery surface of the PWS film caused by the moisture absorption of excess D-sorbitol. S11b, d. The PWS films are adhesive even to wet skin. The PWS film can have an adhesive force of 0. The adhesion reduction on the skin is mainly due to the dirt like sebum. After the contamination is removed by wiping the skin and the PWS electrode with a clinical-grade isopropyl alcohol swab, the adhesion is restored Supplementary Fig.

Hence, the PWS films can be used as a dry electrode repeatedly. The impedance of the PWS films on skin is much lower than the stretchable dry electrodes in literatures 2 , 13 Supplementary Table S1. Compared with highly conductive nanocomposite electrodes with metal nanoparticles or nanowires, the PWS electrodes show significantly lower skin-contact impedance, although the conductivity of the latter can be lower than the former 41 , This is because the impedance is mainly related to the electrode—skin contact instead of the conductivity of the electrode material.

Those dry electrodes in literature do not have the other merits of the PWS films, such as the mechanical stretchability and the self-adhesiveness. In addition, the impedance of the PWS films on skin hardly changes over a long period Supplementary Fig. The impedance is then quite stable over time. Therefore, the PWS films can be used as dry electrodes for long-term healthcare monitoring.

The PWS films can be used as wearable dry electrodes to detect epidermal biopotentials. The noise of the ECG signal can be evaluated by the root-mean-squared RMS analysis, which indicates the fluctuations of the signal over time. It is also much lower than that of other dry electrodes in the literature Supplementary Table S1. The signal quality is also much better than the present dry electrodes using PEDOT or nanocomposites Supplementary Table S1 2 , 13 , 16 , 17 , 24 , 52 , 53 , 54 , 55 , 56 , ECG signals were detected during body movement.

The body movement was induced by firmly attaching a disc-shaped electromechanical vibrator on the skin Fig. The vibrator induced a mean swing amplitude of about 1. The vibration of the skin under the PWS electrode depends on its distance from the vibrator.

When the distance d is smaller, the skin vibration is more vigorous. The motion artifacts are related to the adhesiveness of the dry electrodes. The baseline fluctuations and the noise are even worse when the vibrator is further closer to the electrode.

When a PWS film is attached to the skin, it is stretched during the skin movement, such as driven by wrist bending or twisting, which only slightly affects the resistance and adhesion of the PWS electrode Supplementary Fig.

S18 , as the accurate measurement on the wet and sweaty skin is also a concern for long-term healthcare monitoring. The ECG signal on wet skin is almost the same as on dry skin. ECG signals can be recorded even when the PWS electrodes attached to the wrist and opisthenar were immersed in water Supplementary Fig. The PWS films can further be used as dry electrodes for EMG that detects the action potential generated by the muscle fibers.

When the hand gripes a ball, the wrist flexors contract and generate EMG signals. Different forces are applied to gripe three elastomer balls with the moduli of 0. The corresponding gripping forces imposed on the balls were measured using a commercial optoforce sensor Optoforce 3-axis force sensor Supplementary Fig.

The three balls had different moduli of 0. The peak-to-peak amplitude and the signal intensity are consistent with the gripping force Fig. The detection of EMG signals for muscle motion can have essential applications in the human—machine interfaces.

Apart from the significant motion of a bicipital muscle, the PWS electrode can also detect the low-amplitude EMG signal produced by a finger performing flexion or extension Fig. Compared with ECG and EMG, recording high-quality EEG signals is much more challenging due to the weak signal strength in the microvolts range, interference of scalp, and dense hair. In order to achieve decent contact with the hairy scalp, a 3D PWS dry electrode with vertical pillars was fabricated Fig.

The pillars do not enhance the adhesiveness but can penetrate through the dense hair to contact the scalp. To avoid auditory interferences, the volunteer sat in a comfortable position and relaxed by listening to the white noise.

The potentials triggered by the optic nerves during the opening and closing of the eyes were detected. In contrast, when the eyes are opened, the EEG signals have a broader frequency range. The EEG waves are sensitive to the external sound stimuli.

To capture the auditory response, the volunteer sat in a comfortable position and blindfolded to avoid visual interferences. While the eyes were closed, a loud bell was rung at random intervals, and the perturbed EEG signal with different frequency range was captured as responding to the auditory stimuli Fig.

The PWS dry electrodes were further mounted on a patient with atrial fibrillation in a clinic setting to examine the ability of the PWS dry electrodes in identifying electrocardiographic arrhythmia, detecting brief but significant increases in muscle activity during deep tendon reflex testing, and detecting sustained muscle activity during contraction against resistance and during relaxation.

In addition, the EMG signals can be used to diagnose the muscle functions of neurological patients. When the biceps were triggered by tapping on the biceps tendon, the PWS dry electrodes sensitively recorded an immediate increase in muscle activity induced by contraction Fig. In another clinical testing, the patient tried to lift his forearm under the pulling of biceps contraction while an incremental external force was applied continuously on his forearm.

In this case, an increase in muscle activity persisted during the continuous contraction of the biceps. The PWS dry electrode mounted on the biceps can accurately detect the increment of the EMG signal during continuous contraction and the signal decline in the following relaxation Fig.

These results suggest the ability of the PWS electrodes to quantify muscular strength for neurological assessments in clinical. The PWS electrodes have high conductivity, high mechanical stretchability, excellent adhesiveness to skin and excellent biocompatibility.

They are different from other dry electrodes in literature. Nanocomposites with conductive nanofillers in the elastomer matrix can have high stretchability and high conductivity 41 , and they have been studied as dry electrodes for epidermal biopotential measurement 13 , 16 , 59 , However, the nanocomposite dry electrodes usually give rise to much higher electrode-skin impedance than the PWS electrode because the conductive nanofillers are the minority in the nanocomposites and their effective contact area to skin is thus actually very small In addition, they are usually not adhesive, and thus high motion artifacts can be observed.

Another concern is the possible toxicity of the nanofillers. For example, Bao et al. They can give rise to high motion artifacts due to the poor skin-electrode contact during body movement 52 , 64 , In addition, additives like ionic liquids 66 are toxic, so that PEDOT:PSS added with ionic liquids cannot be used for epidermal biopotential measurement. Although other stretchable PEDOT:PSS composites were used as the dry electrodes, they are not adhesive and thus give rise to high noise during body movement.

Some soft adhesive electrodes were reported in literature 59 , For instance, ultrathin electrodes can be adhesive to skin. But they are difficult to handle, and high noise was observed during body movement. Apart from dry electrodes, conductive hydrogels were investigated as adhesive electrodes as well Refund will be given as.

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