Dae-Hyeong Kim’s research while affiliated with Institute for Basic Science and other places

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Publications (253)


Design strategies of cardiac patch with heterogeneous hydrogel interface and elastomeric surface. a) Schematic illustration of the implemented cardiac patch on a rat heart. b) Bifacial cardiac patch design realized by integrating heterogeneous hydrogels in a single layer, layered with elastomeric nanocomposite outface. c) Exploded view of the cardiac patch, detailing each component: (i) cysteamine‐integrated polyacrylamide adhesive hydrogel, (ii) elastomeric nanocomposite comprising conductive core and encapsulation, (iii) conductive hydrogel composed of cysteamine‐modified Ag–Au NWs, and (iv) hydrophobic SEBS slippery layer.
Schematic illustration detailing the fabrication process of the cardiac patch. a) Ag core‐Au shell nanowire synthesis process and use of nanowires in preparation of (i) nanocomposite solution and (ii) conductive hydrogel solution. b) Fabrication of elastomeric nanocomposite by blade coating and TMSPMA posttreatment. c) Bifacial patch fabrication by curing adhesive hydrogel on the SEBS layer. d) Assembly of bifacial cardiac patch.
Electrochemical characterization of cardiac patch. a) SEM images of interfaces between nanocomposite and encapsulation (left), nanocomposite and conductive hydrogel (right). b) Impedance of conductive hydrogel, nanocomposite, and adhesive hydrogel. c) Cyclic voltammetry of conductive hydrogel and nanocomposite and d) charge storage capacity of each component (n = 3, NC = 9.86 ± 3.07 mC cm⁻², CH = 125.21 ± 19.30 mC cm⁻²; ***p ≤ 0.001 for variables of significance). e) Current density of conductive materials induced by voltage pulse and f) charge injection capacity of each (n = 3, NC = 1.42 ± 0.66 mC cm⁻², CH = 2.09 ± 0.38 mC cm⁻²). Error bars in bar graphs are the standard deviation of the measurements. g) Schematic illustration of cyclic stretching test setup and h) cyclic test results.
Mechanical characterization of the cardiac patch. a) Schematic illustration of bifacial patch and b) SEM images of seamless contact between SEBS layer and adhesive hydrogel. c) Contact angle analysis results of bifacial patch for each side. d) Illustration describing the tissue bonding mechanism of the adhesive hydrogel. e) FTIR spectrograms of polyacrylamide hydrogel (PAAm) and adhesive hydrogel. f) Lap‐shear test results of PAAm (n = 3, 2.63 ± 0.48 kPa) and adhesive hydrogel (n = 4, 40.91 ± 13.6 kPa). g) Stress–strain curves and h) calculated elastic modulus of cardiac patch components: adhesive hydrogel (n = 4, 6.41 ± 1.6 kPa), bifacial patch (n = 4, 40.04 ± 19.3 kPa), conductive hydrogel (n = 4, 46.94 ± 23.9 kPa), and nanocomposite (n = 3, 3895 ± 3650 kPa). *p ≤ 0.05, **p ≤ 0.01 for variables of significance.
Cardiovascular application of cardiac patch for various disease models. a) Schematic illustration demonstrating electrode array mounted on the rat heart. The right image describes the anatomical location of each electrode. b) Optical image of the cardiac patch on the epicardial surface. c) 3‐Channel epicardial electrogram of the normal heart (left) and myocardial infarction (MI) heart (right). d) QRS duration of the rat heart before (black) and after MI induction (red) (n = 5; **p ≤ 0.01, ***p ≤ 0.001 for variables of significance). e) Propagation delay of the epicardium with Channel 3 at the left ventricle (LV) apex as the reference (n = 5; ***p ≤ 0.001 for variables of significance). f) 3‐Channel epicardial electrogram of the heart under bradycardia, pacing, and post‐pacing.

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Soft Cardiac Patch Using a Bifacial Architecture of Adhesive/Low‐Impedance Hydrogel Nanocomposites and Highly Conductive Elastomer Nanocomposites
  • Article
  • Full-text available

December 2024

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7 Reads

Jeeyoung Kim

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Gi Doo Cha

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Minsung Kim

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[...]

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Dae‐Hyeong Kim

Soft implantable multichannel cardiac electrode arrays that establish direct monolithic interfaces with the heart are key components for advanced cardiac monitoring and electrical modulation. A significant technological advancement in this area is the development of stretchable conductive nanocomposites, fabricated through the integration of metallic nanomaterials and elastic polymers, aimed at achieving both high electrical conductivity and mechanical elasticity. Despite these advances, further progress in material performance and device designs is required to ensure seamless, reliable, biocompatible, and high‐fidelity cardiac interfacing. Herein, the development of a soft multichannel cardiac patch based on a bifacial architecture of adhesive/low‐impedance hydrogel nanocomposites and highly conductive elastomer nanocomposites is reported. The bifacial design facilitates the integration of the cardiac patch between the heart and other tissues/organs can be achieved. The hydrogel nanocomposite layer, positioned on the epicardial side, provides stable adhesion to the target cardiac tissue and enables low‐impedance biocompatible interfacing with the heart, while the elastomer nanocomposite layer, positioned on the opposite side, offers high electrical conductivity for facile electrophysiological signal transfer and a low‐friction surface minimizing unwanted interactions with surrounding tissues. The effectiveness of this bifacial patch in multiple applications involving various cardiac signal recordings and electromechanical modulation demonstrations is showcased.

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Soft Implantable Bioelectronics for the Management of Neurological Disorders and Cardiovascular Diseases

October 2024

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36 Reads

Korean Journal of Chemical Engineering

Continuous monitoring systems that effectively manage neurological disorders and cardiovascular diseases are crucial for enhancing the quality of life in aging societies. Soft implantable bioelectronics, which consists of soft devices with mechanical properties akin to biological tissues, are promising candidates for such monitoring systems. These devices enable conformal integration with target tissues, minimizing adverse side effects during their long-term use. They also precisely monitor physiological conditions, facilitating tailored therapeutic interventions based on individual physiological responses. This review highlights recent advancements in soft implantable bioelectronics for managing neurological disorders and cardiovascular diseases. Specifically, strategies for the materials, device fabrication, and their integration with the biological tissues are reviewed in detail first. Then, the challenges in translating these technologies into practical applications are addressed, including the integration of artificial intelligence (AI) technologies.


Inspiration from Visual Ecology for Advancing Multifunctional Robotic Vision Systems: Bio‐inspired Electronic Eyes and Neuromorphic Image Sensors

October 2024

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93 Reads

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1 Citation

In robotics, particularly for autonomous navigation and human–robot collaboration, the significance of unconventional imaging techniques and efficient data processing capabilities is paramount. The unstructured environments encountered by robots, coupled with complex missions assigned to them, present numerous challenges necessitating diverse visual functionalities, and consequently, the development of multifunctional robotic vision systems has become indispensable. Meanwhile, rich diversity inherent in animal vision systems, honed over evolutionary epochs to meet their survival demands across varied habitats, serves as a profound source of inspirations. Here, recent advancements in multifunctional robotic vision systems drawing inspiration from natural ocular structures and their visual perception mechanisms are delineated. First, unique imaging functionalities of natural eyes across terrestrial, aerial, and aquatic habitats and visual signal processing mechanism of humans are explored. Then, designs and functionalities of bio‐inspired electronic eyes are explored, engineered to mimic key components and underlying optical principles of natural eyes. Furthermore, neuromorphic image sensors are discussed, emulating functional properties of synapses, neurons, and retinas and thereby enhancing accuracy and efficiency of robotic vision tasks. Next, integration examples of electronic eyes with mobile robotic/biological systems are introduced. Finally, a forward‐looking outlook on the development of bio‐inspired electronic eyes and neuromorphic image sensors is provided.


Feline eye-inspired artificial vision for enhanced camouflage breaking under diverse light conditions

September 2024

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38 Reads

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3 Citations

Science Advances

Biologically inspired artificial vision research has led to innovative robotic vision systems with low optical aberration, wide field of view, and compact form factor. However, challenges persist in object detection and recognition against complex backgrounds and varied lighting. Inspired by the feline eye, which features a vertically elongated pupil and tapetum lucidum, this study introduces an artificial vision system designed for superior object detection and recognition in a monocular framework. Using a slit-like elliptical aperture and a patterned metal reflector beneath a hemispherical silicon photodiode array, the system reduces excessive light and enhances photosensitivity. This design achieves clear focus under bright light and enhanced sensitivity in dim conditions. Theoretical and experimental analyses demonstrate the system’s ability to filter redundant information and detect camouflaged objects in diverse lighting, representing a substantial advancement in monocular camera technology and the potential of biomimicry in optical innovations.


Recent Advances in Hydrogel‐Based Soft Bioelectronics and its Convergence with Machine Learning

September 2024

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73 Reads

Recent advancements in artificial intelligence (AI) technologies, particularly machine learning (ML) techniques, have opened up a promising frontier in the development of intelligent soft bioelectronics, demonstrating unparalleled performance in interfacing with the human body. Hydrogels, owing to their unique combination of biocompatibility, tunable mechanical properties, and high water content, have emerged as a versatile platform for constructing soft bioelectronic devices. Functionalized hydrogels, such as conductive hydrogels, can efficiently capture biosignals from various target tissues while seamlessly forming conformal and reliable interfaces. They can also function as an intermediary layer between biological tissues and soft bioelectronics for diagnosis and therapy purposes. Meanwhile, ML has demonstrated its efficacy in processing extensive datasets collected from the bioelectronics. The convergence of hydrogel‐based soft bioelectronics and ML has unlocked a myriad of possibilities in unprecedented diagnostics, therapeutics, and beyond. In this review, the latest advances in hydrogel‐based soft bioelectronics are introduced. After briefly describing the materials and device strategies for high‐performance hydrogel bioelectronics, how ML can be integrated to augment the functionalities is discussed. Recent examples of ML‐integrated hydrogel bioelectronics are then discussed. Finally, the review is concluded by introducing future potential applications of AI in hydrogel‐based bioelectronics, alongside inherent challenges in this interdisciplinary domain.




Fabrication of wAu‐CSHs using a sequential formation method. a) Schematic illustration describing the low electrical conductivity of conductive hydrogel nanocomposites. b) Schematic illustration of the conductive hydrogel nanocomposite reported in this study (wAu‐CSH). W‐AuNSs establish a percolation network inside wet hydrogel matrices even under stretched states. c) Schematic illustrations of the sequential formation method for wAu‐CSHs. d) SEM image and optical image (inset) of wAu‐PAAm CSH. e) SEM‐EDS images of wAu‐PAAm CSH. f) Optical images of wAu‐PAAm CSH before (left) and after (right) stretching up to 300% tensile strain. g) Comparison of the conductivity and stretchability of wAu‐CSHs with other conductive hydrogels reported in the literature. Stretchability is displayed only for the conductive hydrogels with conductivity over 10 S cm⁻¹. The legends indicate the type of the conductive component employed. “Combined” means two or more types of conductive components are employed. The list of the references is included in Table S1 (Supporting Information).
Compatibility of W‐AuNSs with the sequential formation method. a) SEM images of wAu‐PAAm CSH before and after stretching. b,c) Optical images of AgNW‐PAAm CSH (b) and AuNS‐PAAm CSH (c) before and after stretching. d) SEM images and optical images (inset) of the dry W‐AuNS network (left), dry AgNW network (middle), and dry AuNS network (right). e) Volume fraction of metal nanomaterials in the dry network of W‐AuNS (black), AgNW (red), and AuNS (blue) (n = 6, each). f) Stress‐strain curve of wAu‐PAAm CSH, AgNW‐PAAm CSH, and AuNS‐PAAm CSH. g) Resistance change (R/R0; R0: initial resistance, R: instantaneous resistance) of wAu‐PAAm CSH, AgNW‐PAAm CSH, and AuNS‐PAAm CSH under tensile strain. h) R/R0 at 30% strain of wAu‐PAAm CSHs (black) and AuNS‐PAAm CSHs (blue) (n = 4, each). Box plots represent the interquartile range, median, maximum, and minimum values of a dataset.
Electrical and mechanical properties of wAu‐CSHs. a) Electrical conductivity and R/R0 at 50% strain of wAu‐CSHs (n = 4). b) Conductivity change (σ/σ0; σ0: initial conductivity, σ: conductivity measured at different time points) of wAu‐PVA CSHs (n = 4) over immersion time in water. Insets are optical images of a wAu‐PVA CSH before and after immersed in water for 3 days. c) R/R0 of wAu‐CSHs under tensile strain. d) Stress‐strain curves of wAu‐CSHs and corresponding bare hydrogels. e) Modulus and maximum strain of wAu‐CSHs and corresponding bare hydrogels (n = 4, each). f) Fabrication process for wAu‐CSHs made of compressed dry W‐AuNS network. t0 indicates the initial thickness of the dry W‐AuNS network, and t indicates the thickness of the dry W‐AuNS network after compressed. g) Conductivity (red) and stretchability (black) of wAu‐CSHs made of compressed dry W‐AuNS network. Stretchability enhancement (blue) of wAu‐CSHs by adding a supporting hydrogel layer. Box plots represent the interquartile range, median, maximum, and minimum values of a dataset.
Fabrication and characterization of wAu‐adhesive CSHs. a) Composition of adhesive hydrogel solution and schematic illustration of adhesion formation between wAu‐adhesive CSH and tissue. b) Electrical conductivity (inset) and stretchability of wAu‐adhesive CSH (n = 5). c) Stress‐strain curve of wAu‐adhesive CSH with supporting hydrogel layer. d) Optical images of adhesive hydrogel and wAu‐adhesive CSH adhering to porcine skin and heart. e) Adhesive strength and interfacial toughness of adhesive hydrogel and wAu‐adhesive CSH (n = 4, each) to porcine skin and heart. f–h) Electrochemical properties of wAu‐SEBS (black) and wAu‐adhesive CSH (red). Cyclic voltammetry (f), electrochemical impedance spectroscopy (g), and chronoamperometry results (h) in PBS solution. Biphasic voltage pulse (green) is applied to the electrode in chronoamperometry. i) Charge storage capcity (black), impedance at 1 kHz (red), and charge injection capacity (blue) of wAu‐SEBS and wAu‐adhesive CSH (n = 5, each). Box plots represent the interquartile range, median, maximum, and minimum values of a dataset.
Bioelectronics applications of wAu‐adhesive CSHs. a) Schematic illustrations of in‐vivo experiments using bioelectrodes. Every experiment is done using both wAu‐SEBS and wAu‐adhesive CSH electrode. b–d) Optical images of wAu‐adhesive CSH electrode placed on rat heart (b) and sciatic nerve (c). The wAu‐adhesive CSH electrode remains adherent to heart (b) and sciatic nerve (d) even when gently pulled. Optical images of wAu‐SEBS electrode are shown in Figure S22 (Supporting Information). e) Epicardial electrogram recordings using wAu‐SEBS and wAu‐adhesive CSH electrode. f) Signal to noise ratio (SNR) of epicardial electrogram recordings using wAu‐SEBS or wAu‐adhesive CSH electrode (n = 6, each; mean ± s.d.). g) Surface ECG recordings under epicardial pacing (0.7 V, 10 ms, 10 Hz monophasic pulse) using wAu‐SEBS or wAu‐adhesive CSH electrode. h) Threshold voltage of epicardial pacing (1 ms, 10 Hz, monophasic pulse) using wAu‐SEBS or wAu‐adhesive CSH electrode (n = 6, each; mean ± s.d.). i) Captured images of ankle joint movement under sciatic nerve stimulation (0.25 V, 1 Hz, biphasic pulse) using wAu‐adhesive CSH electrode. Motion angle (θ) indicates the maximum angular displacement from the initial state. j) θ in response to stimulation voltage (0.15–0.3 V, 1 Hz, biphasic pulse) using wAu‐SEBS or wAu‐adhesive CSH electrode (n = 5, each; mean ± s.e.m.). Statistical significance in (f,h) were analyzed using unpaired t‐test; *P < 0.05, **P < 0.01, ***P < 0.001.
Highly Conductive and Stretchable Hydrogel Nanocomposite Using Whiskered Gold Nanosheets for Soft Bioelectronics

The low electrical conductivity of conductive hydrogels limits their applications as soft conductors in bioelectronics. This low conductivity originates from the high water content of hydrogels, which impedes facile carrier transport between conductive fillers. This study presents a highly conductive and stretchable hydrogel nanocomposite comprising whiskered gold nanosheets. A dry network of whiskered gold nanosheets is fabricated and then incorporated into the wet hydrogel matrices. The whiskered gold nanosheets preserve their tight interconnection in hydrogels despite the high water content, providing a high‐quality percolation network even under stretched states. Regardless of the type of hydrogel matrix, the gold‐hydrogel nanocomposites exhibit a conductivity of ≈520 S cm⁻¹ and a stretchability of ≈300% without requiring a dehydration process. The conductivity reaches a maximum of ≈3304 S cm⁻¹ when the density of the dry gold network is controlled. A gold‐adhesive hydrogel nanocomposite, which can achieve conformal adhesion to moving organ surfaces, is fabricated for bioelectronics demonstrations. The adhesive hydrogel electrode outperforms elastomer‐based electrodes in in vivo epicardial electrogram recording, epicardial pacing, and sciatic nerve stimulation.


Advances in Flexible, Foldable, and Stretchable Quantum Dot Light-Emitting Diodes: Materials and Fabrication Strategies

July 2024

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21 Reads

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1 Citation

Korean Journal of Chemical Engineering

Deformable light-emitting devices, capable of maintaining consistent light emission even under mechanical deformations, represent a cornerstone for next-generation human-centric electronics. Quantum dot light-emitting diodes (QLEDs), leveraging the electroluminescence (EL) of colloidal quantum dots (QDs), show exceptional promise in this domain. Their superior advantages, such as excellent color purity, high luminous efficiency, slim form factor, and facile fabrication on various soft substrates, position them as prime candidates for deformable EL devices. This review explores recent advancements in deformable QLEDs, with a particular focus on material engineering and fabrication strategies. We begin by introducing various types of QDs and the operational principles of QLEDs, along with summarizing performance enhancements in reported deformable devices. Next, we categorize device structures based on the direction of light emission. We then discuss representative methods for patterning QD thin films on flexible substrates to fabricate full-color QLEDs. Additionally, we highlight fabrication strategies for deformable QLEDs with unconventional form factors, including flexible, foldable, fiber-type, and stretchable devices, and their potential applications. We conclude this review with a brief outlook on the future of this technology.


Citations (72)


... The patches were applied in designs by Talbi et al., which allow for controlled drug delivery by varying current density; and the sol-gel patch system for varicose veins of Murari et al. utilizes iontophoresis to manage drug release and penetration through the skin (Murari et al., 2018;Talbi et al., 2018). Moreover, Shin et al. developed an all-hydrogel-based electronic skin (e-skin) patch, integrating various functional hydrogels with electric field stimulation and iontophoresis which accelerated wound healing in vivo (Shin et al., 2024). Another example of iontophoresis-combined application which aissits in wound healing was shown by the enhance of ethosomal piroxicam permeation by iontophoresis in ex vivo rat model by Kazemi et al. (Kazemi et al., 2019). ...

Reference:

Enhancing wound healing through innovative technologies: microneedle patches and iontophoresis
Functional-hydrogel-based Electronic-skin Patch for Accelerated Healing and Monitoring of Skin Wounds
  • Citing Article
  • September 2024

Biomaterials

... The reduction in optical losses at interfaces between materials with differing refractive indices is critical for optimizing the optical performance of various optoelectronic fields, such as light-emitting diodes, photovoltaic devices, image sensors, cameras, transparent glasses, and energy-harvesting [1][2][3][4][5][6][7][8][9][10][11]. To address this issue, multilayer coatings have traditionally been employed as a common method for producing antireflective surfaces. ...

Anti-distortion bioinspired camera with an inhomogeneous photo-pixel array

... By exploiting the differences in the coefficients of thermal expansion between dissimilar adjacent materials, processed patterns and microdevices can be easily picked up under the influence of interfacial thermal stress (Figure 6c). More recently, Shin et al. proposed a non-destructive dry transfer printing strategy based on stress-controlled metal bilayer films during magnetron sputtering [70]. This method successfully transferred metal films and high-temperature treated compound films onto flexible or stretchable substrates, enabling the fabrication of two-dimensional flexible electronic devices and three-dimensional multifunctional devices. ...

Damage-free dry transfer method using stress engineering for high-performance flexible two- and three-dimensional electronics

Nature Materials

... Gallium, which transitions between solid and liquid states at relatively low temperatures (~29.8 • C), provides mechanical reinforcement without sacrificing the stretchability of the hydrogel. This approach builds on recent studies that used gallium in flexible devices for tunable stiffness [21][22][23][24]. ...

Needle‐Like Multifunctional Biphasic Microfiber for Minimally Invasive Implantable Bioelectronics

... With the development of biotechnology and nanotechnology in recent years, a number of new research directions have emerged, such as the use of biomaterials to create bionic eyes, the development of more advanced electronic prostheses, and the combination of external computers and neural interfaces [32]. ...

Avian eye-inspired perovskite artificial vision system for foveated and multispectral imaging
  • Citing Article
  • May 2024

Science Robotics

... At the core of these changes in both form and functionality, the development of soft electrodes has emerged as a pivotal factor. [1][2][3][4][5][6][7][8][9][10][11][12][13] Therefore, substantial research endeavors have been devoted to realizing this vision, yielding the remarkable technical advances and the commercialization of innovative products. In particular, soft electrodes based on electrically and/or electrochemically active organics or carbon-based components (i.e., carbon nanotubes (CNTs) and graphene) have exhibited significant promise, offering cost-effective and highly flexible devices. ...

Stretchable Functional Nanocomposites for Soft Implantable Bioelectronics
  • Citing Article
  • May 2024

Nano Letters

... At present, significant advancements have been achieved in the application of quantum dot-polymer materials in backlight display, particularly in quantum dot-enhanced liquid crystal displays (QLED) and quantum dot backlight units (QBLUs), which can offer a broader color gamut, higher luminance, and longer service life [119][120][121][122]. Through optimizing the size, composition, and surface modification of quantum dots, as well as the structure and performance of polymer substrates, researchers have continuously enhanced the performance of these materials, making their application in high-end display devices more mature and widespread [123,124]. ...

Intrinsically stretchable quantum dot light-emitting diodes

... The impedance of hydrogel electrodes in WNIs refers to the resistance these electrodes offer to the flow of alternating current across various frequencies during neural recording or stimulation ( Fig. 2A) [95,96]. In devices like electroencephalogram (EEG) monitoring systems, the impedance of the electrode directly affects the signal quality. ...

Low-impedance tissue-device interface using homogeneously conductive hydrogels chemically bonded to stretchable bioelectronics

Science Advances