Headphones are an iconic human interface. Current and forthcoming generations of headphones or auricular bioelectronics have capabilities that will fundamentally change how we approach health diagnostics, clinical intervention, and communications. The design of headphones can be traced back to the 1890’s, when Earnest Mercadier developed binaural diaphragms enabling handsfree operation for telephone operators controlling switchboards (Figure 1A) (Mercadier, 2024). A couple decades later Nathaniel Baldwin is credited with inventing the first audio headphones designed to enhance naval communications aboard large and noisy ships. Marking an application transition from their industrial use in communications to personal entertainment use in the audio industry, John Koss designed the first stereo headphones for listening to music in 1958. Since, electrical, mechanical, and biomedical engineering advances have enabled headphone miniaturization, microphone and biometric sensor integration, wireless connectivity, incorporation of digital signal processors (DSP) for active noise cancellation (ANC), audio filtering, amplification, spatial audio encoding, and medical device embodiments for the treatment of health conditions (Figures 1B–D). Today, given their global use in daily communication and digital media consumption, we recognize headphones as being deeply connected to our inner thoughts and emotions, lifestyle, and productivity (Lieberman et al., 2022; Molesworth et al., 2013). As such, headphones and devices intended to be worn on the ear have inspired the design and engineering of modern bioelectronic devices intended for health, medicine, and communications.

The medical device and personal electronics industries have begun to witness barriers blurred as health agencies, care providers, consumers, and patients, motivated by health monitoring, data analytics, and predictive algorithms have begun to integrate wearables into our daily lives (Haghi et al., 2017; Muzny et al., 2020; Perez-Pozuelo et al., 2020; Channa et al., 2021). Markets suffer from no shortage of low-power consumption, wireless connected, multimodal sensor integrated clinical grade and consumer health wearables measuring heart rate, heart rate variability, respiration rate, sleep and activity patterns, metabolic activity, stress levels, and oxygen levels. Over the past decade, a great race for data-driven, predictive insights afforded by modern machine learning (M/L) and artificial intelligence (AI) methods has attracted additional engineering resources around wearable electronic research and development (Acosta et al., 2022; Nahavandi et al., 2022). Many engineers, scientists, and members of the semiconductor and microelectronics industries have risen to challenges in wearable design, testing, packaging, and manufacturing of a bewildering array of batteries, energy harvesters, microprocessors, MEMS accelerometers, optical, electrical, and acoustic sensors fueling growth in consumer and medical wearables (Iqbal et al., 2021; Mamdiwar et al., 2021; Sreenilayam et al., 2020; Hasan et al., 2021).

Developing wearable electronics that have a size, weight, and power profile sufficient for wearing as headphones has some unique engineering challenges. Physical acoustic constraints combined with the fact that people have ears of different sizes and shapes presents other challenges (Møller, 1992; Møller et al., 1995; Poldy and Borwick, 2001). However, the consumer audio, cochlear implant, and hearing aid industries have solved many of these challenges over the past couple decades (Zeng et al., 2008; Chung, 2004; Edwards, 2007; Sabin et al., 2020). In fact, the FDA has recently cleared several over-the-counter (OTC) hearing aids that are now widely available to patients without the need to be fitted by an audiologist (Sabin et al., 2020; Knoetze et al., 2024; Sheng et al., 2024; F. D. A. Commisioner Office, 2024a). More recently in another innovative step forward, the FDA cleared Apple’s AirPods Pro 2 consumer headphones as an OTC hearing aid software through a de novo Software as a Medical Device (SaMD) regulatory pathway (F. D. A. Commissioner Office, 2024; Apple, 2024).

Other advances in flexible and conformable electronics, as well as polymer materials for skin-device interfaces have enabled the development of sophisticated auricular bioelectronics embodied as headphones capable of sensing biochemical and physiological activity (Figures 1C, D) (Qian et al., 2017; Masè et al., 2020; Röddiger et al., 2022). The fields of neuromodulation and bioelectronic medicine have meanwhile been developing various methods of stimulating auricular branches of cranial and cervical nerves for various outcomes (Kaniusas et al., 2019; Verma et al., 2021; Kim et al., 2022). For example, various vibrotactile and electrical forms of transcutaneous auricular vagus nerve stimulation (taVNS) have been shown to reduce inflammation including neuroinflammation associated with long COVID, reduce stress, improve sleep, decrease depression and anxiety, and enhance learning, cognition, and neurorehabilitation as further discussed below. Collectively these advances have produced a climate where the development of open- and closed-loop auricular bioelectronics will produce a new generation of medical devices, health and performance wearables, and brain-computer interfaces (BCIs) that are as scalable as personal headphones. The goal of this perspective is to highlight the anatomy, physiology, and recent engineering milestones enabling the development of modern auricular bioelectronics.

The structure of the auricle or external ear serves mammals unique physiological roles and is tied closely to our evolution and survival (Webster, 1966; Le Maître et al., 2020). The external ear is a cartilaginous structure that has dense vasculature and sensorimotor innervation to help foster heat dissipation, sound location, and positional awareness. The structure of the external ear has two essential parts, which are the pinna and the external auditory meatus (EAM) or outer ear canal ending at the tympanic membrane where the middle ear begins (Figure 2A). This location provides proximal access to the brain, which is useful for recording brain activity as discussed below. The pinna has many distinct anatomical features, which filter and direct sounds to the EAM as illustrated in Figure 2A, The EAM directs and conducts these sound waves to the middle ear before transmitting them to the inner ear for auditory transduction and processing.

The external ear is innervated by two sensory cervical (C2-3) brachial nerves known as the great auricular nerve (GAN) and the lesser occipital nerve (LON; Figure 2B). It is also innervated by three different sensory cranial nerves (CN), which are the eighth CN nerve or facial nerve (CN VIII), branches of the third branch of the fifth CN nerve (CN V3) via the auriculotemporal nerve (ATN), and auricular branches of the vagus nerve (ABVN) originating from the superior ganglion of the 10th CN nerve or vagus (CN X). These sensory nerves have overlapping distributions throughout the skin of the ear differentially innervating the helix, concha, fossa, tragus, lobule, EAM, and other regions (Figure 2B). They also serve common functions, such as mediating physiological reflexes and gating neurophysiological arousal via the ascending reticular activating system (Magoun, 1952; Urbin et al., 2021). For example, ABVN innervation of the EAM serves the anatomical basis for Arnold’s cough reflex (Ryan et al., 2014; Tekdemir et al., 1998; Gupta et al., 1986). The EAM is also innervated by branches of the ATN and facial nerve (Figure 2B), which reflects their close functional relationship in underlying the mammalian diving reflex (Andersen, 1963; Gooden, 1994; Lin, 1988; Panneton and Gan, 2020) and trigemino-cardiac reflexes (Khurana et al., 1980; Lapi et al., 2016; Schaller, 2004). Stimulation of the ABVN can also trigger anti-inflammatory responses by modulating cytokine activity (Wu et al., 2023; Salama et al., 2020; Seitz et al., 2022; Tynan et al., 2021). Given these and other effects discussed below, methods and devices for stimulation of peripheral nerves of the external ear have broad biomedical utility (see below, Methods and Effects of Auricular Neuromodulation).

The vascular structure of the external ear includes a rich arterial supply, as well as dense venous and lymphatic drainage system. Several types of perivascular sympathetic and parasympathetic nerve fibers regulate the vasomotor activity of the ear (Cakmak et al., 2018). The external ear receives its primary blood supply from the superior anterior auricular artery, a branch of the external carotid artery. This artery is essential for providing blood to most parts of the external ear, including the anterior and inferior aspects (Figures 2C, D). Additionally, the superior auricular artery serves as a connection between the superficial temporal artery and the middle anterior auricular artery, ensuring a robust collateral blood flow to the ear in case of reduced blood supply from one source. The anterior auricular branch of the superficial temporal artery specifically supplies the anterior portion of the external ear. Further vascularization comes from the occipital artery, which contributes blood to the posterior region of the external ear. The EAM receives blood from both the inferior auricular artery and the auricular branches of the maxillary and superficial temporal arteries (Figures 2C, D). Venous drainage closely follows the arterial supply, with the veins of the external ear running alongside the corresponding arteries. This arteriovenous network is believed to play a major role in thermoregulation. Venous flow from the EAM drains into the pterygoid plexus, external jugular vein, and maxillary vein.

Lymphatic drainage of the external ear is achieved through four primary lymphatic vessels (Pan et al., 2011). The anterior region of the ear is drained by lymphatic branches that converge into a single vessel, which then flows into the pre-auricular lymph nodes. Lymphatic vessels from the superior aspect of the helix may travel along the anterior part of the ear, ultimately reaching the infra-auricular lymph nodes. Similarly, vessels originating in the scaphoid fossa, adjacent to the auricular tubercle, form the middle branches that drain the anterior region of the external ear, also converging toward the infra-auricular nodes. Finally, the lobular branches begin as a network of vessels in the auricular lobule. These vessels merge and drain toward the infra-auricular lymph nodes, forming an organized system of lymphatic drainage across the external ear. The unique anatomy and physiology of the external ear, including its rich vasculature, diverse sensory innervation, and proximity to the brain, make it an ideal location for recording physiological, biochemical, and brain activity data, while also providing an accessible site for stimulating nervous system activity as discussed below.

A major challenge for bioelectronic devices arises from material incompatibility between hard charge carriers (i.e., metal electrodes) and the soft, irregular surface of the skin. Conductive hydrogels, polymers, and biomedical adhesives have been developed to possess skin-like mechanical and electrical properties thereby mitigating many issues encountered when interfacing bioelectronic devices with the body (Iqbal et al., 2021; Keplinger et al., 2013; Lim et al., 2021; Yuk et al., 2019; Li et al., 2023). Hydrogels and conductive polymers have proven particularly advantageous in neuroengineering through the development of soft bioelectronics for neural sensing and neuromodulation interfaces (Jeong et al., 2015; Sunwoo et al., 2020; Zhao et al., 2024). Due to their low melting points and other physicochemical properties, liquid metals for the engineering of flexible, stretchable, and wearable electronics have opened new possibilities in bioelectronics (Deng et al., 2024). Liquid metals printed onto or incorporated into different hydrogel and polymer substrates have enabled the development of electric skin, tattooable circuits, neural interfaces, electronic vessels, and soft thermoelectric heaters (Iqbal et al., 2021; Sreenilayam et al., 2020; Deng et al., 2024; Park et al., 2019; Zhao et al., 2023a).

Coating, spinning, or impregnating natural and synthetic fibers with electric inks and conductive polymers has led to the development of electronically active, smart textiles and fabrics for wearable bioelectronics (Baeg and Lee, 2020; Ismar et al., 2020). These innovations in E-textiles have improved the comfort of devices since conducting metal fibers historically used create uncomfortable sensations against the skin despite their superior electrical conductivity. Carbonized nanoparticles and nanocomposites are presenting interesting approaches to the development of wearable electronic textiles. For instance, chemical vapor deposition of graphene monolayers and transfer from copper substrates has been used to manufacture transparent, flexible graphene fibers capable of serving as textile electrodes (Neves et al., 2015; Fang et al., 2020). Thin piezoelectric films and electroactive papers provide methods of fabricating flexible and conformable mechanically active sensors and actuators, as well as means for energy harvesting and power generation (Khan et al., 2016; Yun et al., 2007; Sezer and Koç, 2021). One interesting application is their use in producing piezoelectric textiles, which pose intriguing possibilities for the future of healthcare and power generation (Atalay et al., 2016; Lund et al., 2018). With the materials, fabrication, and engineering knowledge gained over the last decade in wearable microelectronics, nearly any anatomy can be targeted and affixed with sensors and stimulators that seamlessly integrate hardware with the body. The remainder of this perspective will focus on the human external ear as a target for bioelectronic devices and applications in healthcare, medicine, and communications.

The activity of the vagus nerve underlies core aspects of our health including digestion, cardiovascular reflexes, cardiac activity, immune responses, arousal (sleep/wake, consciousness, and fight/flight/freeze), attention, cognition, learning, and memory. Transcutaneous auricular vagus nerve stimulation (taVNS) involves the non-invasive modulation of auricular branches of the vagus nerve (ABVN; Arnold’s nerve or Adleman’s nerve) located under the skin’s surface of the external ear. Using pulsed electrical currents to modulate ABVN fibers located in different locations of the external ear, this approach has gained attention for its safe ability to modulate autonomic nervous system activity, inflammation, neuroplasticity, attention, stress, learning, mood, and sleep, by altering activity of brain nuclei and neurotransmitters known to regulate these processes such as the locus coeruleus and norepinephrine respectively (Verma et al., 2021; Kim et al., 2022; Urbin et al., 2021; Liu C.-H. et al., 2020; Wang et al., 2021; Butt et al., 2020; Sant'Anna et al., 1992; Tyler, 2017; Tan et al., 2023; Bottari et al., 2024; Srinivasan et al., 2023; Ma et al., 2022; Phillips et al., 2021).

Many methods and devices employing taVNS to date however fall short in providing user comfort due to their reliance on inefficient body-electrode coupling approaches. Discomfort during taVNS manifests as an electrical biting sensation, in part due to electromechanical mismatches between the electrode and skin. High current densities produced by metal electrodes with a small surface area of skin coupling, and metal or rubber electrodes clipped onto the ear create mechanical pinching sensations that are distracting and uncomfortable (Figure 3A). This can be further aggravated by wet coupling methods using saline sprays or electrolyte gels where the microfluidic interface (and local impedance) undergoes frequent fluctuations and distortions between the electrode and skin. For enhancing cognition, reducing stress, or promoting sleep it is critical that the user or patient has a comfortable experience, or the off target, distracting and uncomfortable sensations can override intended taVNS outcomes (Miyatsu et al., 2024; Jigo et al., 2024). In other words, stimulating the external ear with electrical currents can both activate and suppress sympathetic activity (stress) depending on many variables including interface comfort and usability.

To overcome human factors issues associated with taVNS, we developed methods of using low-impedance, conductive polymers and soft hydrogel earbud electrodes or electrode interfaces inserted into the EAM to achieve external ear stimulation (Figure 3B) (Tyler et al., 2019; Tyler et al., 2022). Earbud electrodes comprised of a hydrogel inserted in this location target the ABVN, facial nerve, and auriculotemporal branches of the trigeminal nerve located just under the skin of the walls of the external acoustic meatus (Figures 2B, 3B). These external ear stimulation approaches, using conductive hydrogel earbud electrodes inserted into the EAM, formed the basis of methods used and devices designed to enhance foreign language learning (Phillips et al., 2021; Pandža et al., 2020) and relieve tinnitus symptoms (Figure 4A) (Tyler Richard et al., 2024). A major reason modern bioelectronic devices use hydrogel coupling methods is that they reduce electromechanical mismatches across skin-electrode interface resulting in stable, uniform current distributions, enhanced user comfort, and improved electrical efficiency (Keplinger et al., 2013; Lim et al., 2021; Yuk et al., 2019; Jia and Rolandi, 2020; Liu K. et al., 2020; Yang and Suo, 2018; Fu et al., 2020).

Using hydrogel earbud electrodes to achieve comfortable, bimodal, electro-aural stimulation of the external ear during presentation of notch-filtered audio stimuli was recently shown capable of reducing symptoms associated with tinnitus (Figure 4A) (Tyler Richard et al., 2024). Another study recently compared different methods of VNS on language learning. The authors report that taVNS failed to produce an effect on language learning compared to transcutaneous cervical VNS. Interestingly, Miyatsu et al. (2024) implemented a saline sprayed, conductive rubber, earbud electrode that can produce distracting and uncomfortable sensations (Figure 3A). Any distracting electrical sensations produced by the saline-coupled earbud electrodes used in their study might explain why this specific approach to taVNS failed to produce a significant effect on language learning. Further supporting this interpretation, evidence from earlier studies using hydrogel-coupled earbud electrodes to deliver stimulation from the same device indeed led to significant improvements in foreign language learning (Phillips et al., 2021; Tyler et al., 2019). These observations indicate that future taVNS efforts should focus on optimizing electroconductive hydrogels and polymers for comfortably interfacing with the human ear. These efforts can be combined with work to advance neurostimulation algorithms and parameters for continuing to enhance the electrical sensation experiences, ease of use, user comfort, and efficacy of electrical taVNS. This approach should prove valuable considering recent demonstrations that high-frequency (kHz), sub- perceptual taVNS produces significant changes in the functional connectivity of the prefrontal cortex, cingulate cortex, and insula (Mao et al., 2022).

Supported by a growing body of literature, taVNS has immense clinical potential given its ability to provide drug-free, therapeutic approaches to treating some of our most pressing health concerns. Several clinical studies have shown that taVNS is effective for treating insomnia and poor sleep, which is a major contributor to poor health and chronic disease. In a randomized, placebo-controlled study, Zhang et al. (2023) demonstrated that taVNS significantly improved insomnia scores on the Pittsburgh Sleep Quality Index (PSQI) and the Insomnia Severity Index (ISI), as well as by EEG polysomnography compared to sham controls (Zhang et al., 2023). The effects produced by taVNS on PSQI were equivalent to those produced by a cognitive behavior therapy for insomnia (CBT-I) control. Interestingly however, ISI scores demonstrated taVNS produces a more durable effect than CBT-I in follow-up surveys. Another recent randomized, sham-controlled study showed that 8 weeks of taVNS treatment produced significant improvements in insomnia by PSQI scores and that these improvements were maintained for 12 weeks post-treatment compared to controls (Zhang et al., 2024). Several recent functional neuroimaging studies show the effects of taVNS on insomnia are produced by a significant change in the resting state functional connectivity of thalamus, cingulate gyrus, angular gyrus, precuneus, and prefrontal cortex (Zhao et al., 2020; He et al., 2022; Zhao et al., 2023b). With respect to the impacts of poor sleep on daily brain function, another study showed taVNS significantly improves working memory in sleep deprived, stressed human subjects (Zhao R. et al., 2023). Collectively these studies demonstrate that taVNS embodied as auricular bioelectronic devices can transform healthcare by improving the sleep quality in diverse populations suffering from poor sleep quality and efficiency.

Many studies documenting the impacts of taVNS on mental health and quality of life outcomes are also emerging in the literature. Li et al. (2022) demonstrated that 12-week treatment with taVNS produced significant reductions in major depression measured by Hamilton Depression Rating Scores (HAM-D) that were equal to reductions produced by 12-weeks citalopram treatment in a randomized clinical trial designed to compare their effects (Li et al., 2022). An open-label study has demonstrated the proof-of-concept for reducing HAM-D scores while using taVNS to treat peripartum depression (Deligiannidis et al., 2022). Similarly used to treat depression related to life events, a double-blind, randomized, placebo-controlled study recently demonstrated that taVNS produced significant reductions in HAM-D scores while treating post-stroke depression (Liu et al., 2024). Functional neuroimaging studies investigating the effects of taVNS on depression have shown immediate and robust changes in the functional connectivity of several brain circuits following treatment (Sun et al., 2022; Ma et al., 2022; Guo et al., 2024). Several studies have demonstrated that taVNS also produces functional behavioral outcomes that may underlie some aspects of its ability to treat demoralized or depressed moods by restoring proper regulation of psychophysiological arousal. For example, Ferstl et al. (2024) recently conducted a randomized, sham-controlled study showing that taVNS produces significant improvements in invigoration and wanting in subjects suffering from major depression (Ferstl et al., 2024). Another recent randomized, sham-controlled study demonstrated that taVNS produced significant changes in bottom-up neurophysiological arousal leading to significantly improved impulse control during emotional tasks (Camargo et al., 2024). The changes produced by taVNS in these studies are consistent with those expected, which result in improved motivation and mood. Decreased motivation and blunted affect are not only hallmarks of depression, but they are signs and symptoms of over-worked, exhausted, stressed, and over-burdened people struggling with daily life. Interestingly, taVNS has been shown to significantly improve mood recovery following a period of high effort, physical and cognitive exertion (Ferstl et al., 2022). Moreover, another recent human study demonstrated that taVNS significantly improves the invigoration and motivation to work for rewards (Neuser et al., 2020). These studies collectively indicate that electrical taVNS may impact society by improving the motivation, will, and desire of people to work through periods of high stress, depression, and low morale.

In addition to electrical taVNS, other modes of auricular neuromodulation can be intergraded into headphone style devices. Caloric vestibular stimulation (CVS) involves the thermal modulation of the vestibular system by cooling or heating the ear canal (Figure 4B). In a manner similar to electrical taVNS, studies have shown that CVS can modulate brain activity across different cortical regions (Wypych et al., 2019), regulate mood and affect (Preuss et al., 2014), reduce pain evoked potentials (Ferrè et al., 2015), and modulate sensory perception and conscious experience in healthy and brain-damaged patients (Bottini et al., 1995; Bottini et al., 2005; Bottini and Gandola, 2015). A recent study using a wearable, solid-state device embodied as an aluminum, thermal headphone probe to achieve cyclic CVS was effective at reducing both motor and non-motor symptoms in Parkinson’s disease patients following 8 weeks of at home treatment (Wilkinson et al., 2019). Advances in flexible and wearable thermoelectric materials may offer new headphone design opportunities for CVS in therapeutic neuromodulation applications (Wilkinson et al., 2019; Du et al., 2018). Other materials advances in thermally conductive polymers and use of liquid metals for interfacing thermoelectric materials with the skin can improve thermal transfer and insulation to optimize CVS methods (Deng et al., 2024).

Vibrotactile and haptic stimulation of external ear has also shown to have interesting biomedical applications including to mediate human-computer interactions. Targeting vagal nerves innervating the cymba concha, vibrotactile stimulation of the external ear has been shown to modulate arousal (Tan et al., 2024) and reduce cytokine production of TNF, IL-1β and IL-6 to attenuate systemic inflammation in patients with Rheumatoid arthritis (Addorisio et al., 2019). It has been argued the tactile sensitivity of the external ear has been overshadowed by its auditory functions and that haptic stimulation of the ear represents an opportunity for information transfer (Lee et al., 2019). Lee et al. (2019) demonstrated small ear worn haptic stimulation devices could encode environmentally relevant spatiotemporal information by stimulating six different locations on the external ear. In an adaptive embodiment, ear haptics were demonstrated as a human-computer interface to enhance the experience of virtual reality applications for deaf and hard-of-hearing (DHH) individuals (Mirzaei et al., 2020). Haptic stimulation of the ear can convey sound direction in relation to DHH users during a VR experience when a system was not universally designed and intended for hearing enabled persons using spatially encoded audio to simulate sound distance (Mirzaei et al., 2020). The integration of piezoelectric thin films, piezopolymers, and electroactive papers (Khan et al., 2016) into flexible and conformable auricular haptic bioelectronic devices opens fascinating possibilities for medicine and communications. Not only can these materials provide for the design of active stimulation or neuromodulation devices to be worn in the ear, but they can also serve the basis for a wide range of electrophysiological and biochemical sensors to record data for diverse applications in health monitoring and cognitive enhancement.

In some embodiments, auricular bioelectronic devices have sensors that can detect a wide range of physiological, biometric, and chemical signals such as heart rate or brain activity using electroencephalography (EEG), head orientation, and even metabolic markers like lactate. The development of auricular monitoring devices presents challenges like those discussed above for neuromodulation. Integrating advanced sensor materials into devices intended to be worn in or on the ear while ensuring comfort, durability, and accuracy of them in real-world settings can be difficult. The development and use of hydrogels and dry EEG electrode materials represent significant advances over traditional wet electrodes, which require gels and skin preparation. Advances in these materials, flexible electronics, and additive manufacturing has improved the efficiency and comfort of auricular bioelectronic devices making them suitable for continuous everyday use.

Unlike traditional scalp EEG systems, which rely on wet electrodes and conductive gels to reduce impedance, in-ear systems offer a more user-friendly and comfortable experience. For example, in-ear EEG electrodes can be fabricated using viscoelastic materials (memory foam) and silver-coated fabric electrodes (Figure 5A). This approach allows EEG sensors to fit in the EAM while capturing brain signals such as alpha rhythms, visual evoked potentials (VEPs), steady-state visual evoked potentials, and auditory steady-state responses (Goverdovsky et al., 2017). The approach was also useful for conducting polysomnography or recording brain activity during sleep (Goverdovsky et al., 2017). A more custom approach involves the fabrication of individualized EEG earbud electrodes. Joyner et al. (2024) recently used optical scans of individual patient’s ears to create custom EEG earbud electrodes made from a soft silicon material and conductive polymer-coated silver rivets (Figure 5B). These electrodes were used to monitor epileptic activity in validation studies, which demonstrated the earbuds can provide patients with a discrete and comfortable EEG device for continuous monitoring while offering clinicians reliable and accurate data compared to intracranial and scalp recording methods (Joyner et al., 2024). Beyond this type of clinical diagnostic application, there are opportunities to develop auricular bioelectronics for brain-computer interfaces (BCI’s) and human performance monitoring.

EEG metrics provide insights into how focused or mentally engaged a person may be, making them invaluable for applications in cognitive performance and mental health. By tracking these metrics, auricular bioelectronics can offer real-time feedback on mental states, enhancing both medical and consumer applications. To reach the scalable potential of these approaches however, highly personalized auricular bioelectronics as described above will need to be developed. Another innovative approach towards developing individualized, in-ear bioelectronics was recently demonstrated using spiral shaped, electrothermal actuating electrodes (SpiralE) that conform to the EAM structure of users (Figure 6A) (Wang et al., 2023). Wang et al. (2023) engineered a flexible electrode using double-layer shape memory polymers embedded in an electrothermal actuation layer with an EEG detection top layer comprised of Au wires insulated in polyimide (Wang et al., 2023). This design enabled in-ear EEG electrodes to comfortably conform to the shape of the ear of individual users (Figure 6A), while being worn and used for high fidelity recordings in visual and auditory brain-computer interfaces (BCI’s) (Wang et al., 2023). These studies have shown that the quality of the signal for EEG obtained through auricular approaches is sufficient to monitor many brain states in a manner equivalent to conventional scalp EEG. In addition, by monitoring electrical impedance and heart rate and respiration from one integrated device can improve the reliability of recordings within and across recording sessions. In addition to EEG monitoring, these devices have incorporated various other sensors, including accelerometers for tracking head movements and orientation, as well as biochemical sensors for detecting metabolic markers like lactate during physical activity.

Optical sensors can also be integrated into headphones to record heart rate, SpO2 (blood oxygen saturation), VO_2max and other physiological metrics. These optical sensors use photoplethysmography (PPG) technology to measure blood flow non-invasively, allowing for continuous monitoring of cardiovascular health in auricular bioelectronic devices (Patterson et al., 2009; Leboeuf et al., 2014; Passler et al., 2019). Piezoelectric and MEMS-based sensors capable of detecting heart rate through pressure fluctuations in the ear have also been shown useful for cardiac monitoring (Park et al., 2015; Cui et al., 2022). Advances in thermoforming techniques allow for the creation of custom and generic earpieces that can house multiple sensors while maintaining comfort and stability. Flexible and stretchable materials are used to integrate multiple sensors into a compact design, suitable for long-term wear. Xu et al. (2023) recently developed integrated electrochemical, chronoamperometry sensors with flexible Ag electrodes, which were 3D-printed, coated with a layer of PVA hydrogel, bonded to a flexible PCB, and mounted into an earphone assembly to simultaneously record lactate from sweat and EEG from the ear during exercise (Figure 6B) (Xu et al., 2023). This multimodal sensing approach including biochemical measures from sweat may be useful in monitoring other variables beyond lactate during EEG, HR, and head position. For instance, obtaining measures of stress hormones or drug metabolites continuously to gain insights related to human performance using auricular bioelectronic devices may be particularly useful.

Another exciting area of development in auricular bioelectronics is the integration of spatial audio with sensor data, such as EEG and accelerometry. Spatial audio enhances the auditory experience by simulating how sound moves in the user’s environment. With the help of accelerometers and gyroscopes, which track head movements in real-time, spatial audio can adjust sound orientation based on the user’s head position, maintaining a consistent and immersive auditory experience. This data, combined with EEG monitoring of cognitive load, attention, and engagement can optimize the auditory experience for various activities, such as work, studying, relaxation, focus, or gaming. Wireless in-ear EEG systems, with multi-channel, multimodal recording capabilities will continue to expand the potential for BCIs and neurotechnology. As the capabilities of wearable auricular devices continue to evolve, the integration of both stimulation and sensing functions within a closed-loop system opens new possibilities for real-time neuromodulation, personalized health interventions, and advanced brain-computer interfaces.

Closed-loop, auricular bioelectronics possess transformative potential for neuromodulation by integrating real-time sensing and stimulation capabilities. One prominent application would be for the treatment of atrial fibrillation or arrhythmias, where in-ear sensors can monitor for abnormal heart rhythms while taVNS provides corrective feedback. The sensing of arrhythmic events using PPG or piezoelectric-based heart rate sensors embedded in the ear canal could trigger taVNS to regulate parasympathetic activity and restore normal cardiac rhythms (Kharbanda et al., 2022; Murray et al., 2016; Stavrakis et al., 2020). Similarly, stimulation of vagal or trigeminal fibers may hold potential for treating some forms of sleep apnea and sleep-disordered breathing (Ratneswaran et al., 2023; Chowdhury et al., 2017). In this embodiment, auricular bioelectronics can be engineered to sense abnormal breathing patterns to trigger responsive stimulation of trigeminal and ABVN fibers in the EAM to reduce airway resistance and restore proper respiration during sleep.

There are other promising avenues for closed-loop auricular bioelectronics, such as for the treatment of neuromuscular disorders like Restless Leg Syndrome (RLS) which benefits from taVNS treatments (Hartley et al., 2023a; Hartley et al., 2023b; Merkl et al., 2007). Such an embodiment may include recordings of muscle activity using wireless electromyography (EMG) sensors placed on the legs to detect RLS episodes for triggering taVNS to mitigate symptoms and discomfort. In a similar fashion, EMG sensors placed in auricular bioelectronic devices could detect abnormal activity associated with nocturnal bruxism and responsively trigger taVNS stimulation protocols, which can reduce bruxism severity (Polini and Budai, 2022). Methods for cognitive enhancement and attention regulation with closed-loop auricular bioelectronics are also ripe for development. In-ear EEG sensors capable of monitoring neural activity related to attention and cognitive engagement can be paired with taVNS to enhance vigilance or sustained attention (Tyler, 2017). Cognitive enhancement with closed-loop taVNS has potential applications for treating attention, memory, and learning disorders, as well as for enhancing human performance in high-stakes environments, such as in military, first responder, or aerospace operations, where maintaining optimal cognitive function and decision-making processes under stress is critical (McKinley et al., 2011; Musson et al., 2004; Dhami et al., 2015; Picano et al., 2006).

In human performance enhancement or health applications, closed-loop systems can help regulate stress responses by continuously monitoring physiological and biochemical stress markers. Integrated electrochemical or optical sensors in auricular devices can detect cortisol or other stress hormones, while heart rate variability sensors can report sympathetic tone. When elevated stress is detected, auricular bioelectronic devices can deliver taVNS protocols to reduce sympathetic activity and promote parasympathetic activation thereby dampening stress and improving overall wellbeing. Additionally, the integration of these sensors and stimulation methods with BCIs creates opportunities for enhanced human-computer interactions like accelerating human learning. As auricular bioelectronics advance, they will enable seamless, scalable devices that integrate into our daily lives just like personal headphones do today. The next generation of headphones embodied as auricular bioelectronics will provide for the global delivery of several new medical therapies, human-computer interfaces, and communication technologies.

Auricular bioelectronics are poised to revolutionize healthcare and human performance by providing a versatile, wearable, non-invasive platform for real-time monitoring and neuromodulation. These devices, integrating advanced sensors and stimulation capabilities, hold potential for treating a wide range of conditions, from arrhythmias and sleep apnea to inflammation and cognitive disorders. As material science and flexible electronics continue to advance, auricular bioelectronics will become increasingly dynamic, comfortable, effective, and personalized. With scalable designs akin to personal headphones, these devices are likely to play a significant role in BCIs, offering yet unrealized opportunities for improving health, cognition, and human-machine interactions.

One of the most promising future applications of auricular bioelectronics is to enable the scalable delivery of on-demand, digital immunotherapies to treat acute and chronic inflammation. It is well established that chronic inflammation is a number one cause of disease and death, as well as a major driver of health disparity. By modulating the cholinergic anti-inflammatory pathway, it has been shown that taVNS can reduce acute and chronic inflammation in several conditions (Wu et al., 2023; Salama et al., 2020; Liu et al., 2020a; van Beekum et al., 2022; Kaniusas et al., 2020; Mastitskaya et al., 2021). Embodied as a set of headphones taVNS may provide the ability to replace many over the counter and prescription drugs like non-steroidal anti-inflammatory drugs, steroidal compounds, antihistamines, and others used one to treat inflammation. The integration of these approaches with closed-loop monitoring of cytokines and other inflammatory biomarkers using wearable bioelectronic methods will enable responsive taVNS for real-time, personalized, digital immunotherapeutic devices, which may be capable of disrupting the medical device, pharmaceutical, and consumer health industries (Figure 7).

While auricular bioelectronics hold great promise, several pitfalls and limitations must be addressed for these technologies to achieve their full potential. First, there are challenges associated with overcoming the technological barriers to developing reliable, long-lasting, and comfortable wearable devices. Ensuring the accuracy, reliability, durability of sensors, particularly in real-world environments with variable conditions, is essential for making closed-loop systems robust and effective. Optimizing energy efficiency will require attention since microelectronics require advanced power management systems to enable continuous operation. Several barriers to adoption might be related to the cost and complexity of engineering devices, which may limit access to those who can afford them unless manufacturing and production costs can be minimized. The lack of public understanding of potential risks, benefits, and functions of auricular bioelectronics could cause hesitancy among consumers, patients, and healthcare providers.

From a societal and ethical perspective, data privacy and security will always pose concerns and challenges. Auricular bioelectronics, which continuously collect sensitive biometric and neural data, could pose privacy risks if not properly protected and safeguarded. Another ethical consideration as alluded above is the availability and accessibility of this technology, which could exacerbate existing healthcare disparities if not distributed equitably. Despite these challenges, the next era of technological developments, including continued advances in flexible electronics, packaging, improved sensor algorithms, and improved energy harvesting methods, will drive innovation forward in the development of auricular bioelectronics. It will be critical to form collaborations between medical, research, semiconductor, and regulatory organizations to establish standards and guidelines to ensure auricular bioelectronics are safe, effective, and accessible to a broad range of users. These collaborations will ultimately pave the way for the integration of auricular bioelectronics into everyday healthcare and cognitive performance enhancement.