Lifetime engineering of bioelectronic implants with mechanically reliable thin film encapsulations
Martin Niemiec,
Kyungjin Kim
Abstract:While the importance of thin form factor and mechanical tissue biocompatibility has been made clear for next generation bioelectronic implants, material systems meeting these criteria still have not demonstrated sufficient long-term durability. This review provides an update on the materials used in modern bioelectronic implants as substrates and protective encapsulations, with a particular focus on flexible and conformable devices. We review how thin film encapsulations are known to fail due to mechanical str… Show more
“…[41][42][43] The inorganic encapsulation films present excellent hermeticity, and their limited elasticity (≈1% of crack onset strain) and brittleness (elongation limit of a few percent with Young's modulus on the order of 100 GPa) still can offer impressive bendability onto compliant polymer substrates (e.g., polyethylene terephthalate (PET), polyimide, on the order of 1 GPa [39,44] ) as long as the film thickness is maintained thin. For example, bending 100μm-thick 3 cm-long substrate to a complete circle radius of 5 mm requires only 1% of applied strain based on applied bending strain equation 𝜖app = t/D, comprised of thickness t and diameter of the circle D. [44][45][46] However, the inorganic encapsulation onto elastomer or any soft polymer substrates (<100 MPa [11,47] ) creates extreme elastic mismatch at the interface and can generate mechanical failures (e.g., cohesive cracking [48,65] , substrate cracking, [49] and interfacial delamination [50] ) even at the negligible applied strain (≈0.1%). [51] In the meantime, most organic encapsulation films present insufficient hermeticity where barrier improvement factor is unlikely over 1.…”
Section: Introductionmentioning
confidence: 99%
“…For example, bending 100µm‐thick 3 cm‐long substrate to a complete circle radius of 5 mm requires only 1% of applied strain based on applied bending strain equation ε app = t/D , comprised of thickness t and diameter of the circle D . [ 44‐46 ] However, the inorganic encapsulation onto elastomer or any soft polymer substrates (<100 MPa [ 11,47 ] ) creates extreme elastic mismatch at the interface and can generate mechanical failures (e.g., cohesive cracking [ 48,65 ] , substrate cracking, [ 49 ] and interfacial delamination [ 50 ] ) even at the negligible applied strain (≈0.1%). [ 51 ] In the meantime, most organic encapsulation films present insufficient hermeticity where barrier improvement factor is unlikely over 1.…”
Advances in electro‐ionic soft actuators hold significant potential as next‐generation bioelectronic interfaces due to mechanical compliance and operation in agreement with soft biological tissues and low voltages. However, current devices call for encapsulation strategies to accommodate high mechanical demands and long‐term stability in environmental changes. In this study, a durability of polyvinylidene‐fluoride‐co‐hexafluoropropylene (PVDF‐co‐HFP) honeycomb skeleton electrolyte encapsulated with a biocompatible polyisobutylene (PIB) thin film is being investigated. A low water vapor transmission rate (0.61 g m−2 day−1) and elastic modulus (10 kPa) are measured from a 7.5 µm‐thick thin‐modified PIB‐encapsulation layer. The PIB‐encapsulated soft actuator maintains 68% of its mechanical durability after 40 000 cycles of zero‐to‐tension fatigue loading at room temperature. A cantilever actuation test of the PIB‐encapsulated 3mm‐wide 30mm‐long actuator film shows a large tip displacement (15.90 mm) at a low voltage (±1.5 V) under 0.1 Hz, 37 °C, 50% relative humidity (RH). Most importantly, while the unencapsulated actuator immediately degrades in a few cycles at 37 °C, 50%RH, and 0.1% applied strain, PIB‐encapsulated soft actuator performs up to 6500 dynamic actuation cycles without any functionality degradation. Exceptional durability against mechanical fatigue and stability at elevated temperature and humidity meet the prerequisite for future soft biomedical robots that enable long‐lasting safe operations.
“…[41][42][43] The inorganic encapsulation films present excellent hermeticity, and their limited elasticity (≈1% of crack onset strain) and brittleness (elongation limit of a few percent with Young's modulus on the order of 100 GPa) still can offer impressive bendability onto compliant polymer substrates (e.g., polyethylene terephthalate (PET), polyimide, on the order of 1 GPa [39,44] ) as long as the film thickness is maintained thin. For example, bending 100μm-thick 3 cm-long substrate to a complete circle radius of 5 mm requires only 1% of applied strain based on applied bending strain equation 𝜖app = t/D, comprised of thickness t and diameter of the circle D. [44][45][46] However, the inorganic encapsulation onto elastomer or any soft polymer substrates (<100 MPa [11,47] ) creates extreme elastic mismatch at the interface and can generate mechanical failures (e.g., cohesive cracking [48,65] , substrate cracking, [49] and interfacial delamination [50] ) even at the negligible applied strain (≈0.1%). [51] In the meantime, most organic encapsulation films present insufficient hermeticity where barrier improvement factor is unlikely over 1.…”
Section: Introductionmentioning
confidence: 99%
“…For example, bending 100µm‐thick 3 cm‐long substrate to a complete circle radius of 5 mm requires only 1% of applied strain based on applied bending strain equation ε app = t/D , comprised of thickness t and diameter of the circle D . [ 44‐46 ] However, the inorganic encapsulation onto elastomer or any soft polymer substrates (<100 MPa [ 11,47 ] ) creates extreme elastic mismatch at the interface and can generate mechanical failures (e.g., cohesive cracking [ 48,65 ] , substrate cracking, [ 49 ] and interfacial delamination [ 50 ] ) even at the negligible applied strain (≈0.1%). [ 51 ] In the meantime, most organic encapsulation films present insufficient hermeticity where barrier improvement factor is unlikely over 1.…”
Advances in electro‐ionic soft actuators hold significant potential as next‐generation bioelectronic interfaces due to mechanical compliance and operation in agreement with soft biological tissues and low voltages. However, current devices call for encapsulation strategies to accommodate high mechanical demands and long‐term stability in environmental changes. In this study, a durability of polyvinylidene‐fluoride‐co‐hexafluoropropylene (PVDF‐co‐HFP) honeycomb skeleton electrolyte encapsulated with a biocompatible polyisobutylene (PIB) thin film is being investigated. A low water vapor transmission rate (0.61 g m−2 day−1) and elastic modulus (10 kPa) are measured from a 7.5 µm‐thick thin‐modified PIB‐encapsulation layer. The PIB‐encapsulated soft actuator maintains 68% of its mechanical durability after 40 000 cycles of zero‐to‐tension fatigue loading at room temperature. A cantilever actuation test of the PIB‐encapsulated 3mm‐wide 30mm‐long actuator film shows a large tip displacement (15.90 mm) at a low voltage (±1.5 V) under 0.1 Hz, 37 °C, 50% relative humidity (RH). Most importantly, while the unencapsulated actuator immediately degrades in a few cycles at 37 °C, 50%RH, and 0.1% applied strain, PIB‐encapsulated soft actuator performs up to 6500 dynamic actuation cycles without any functionality degradation. Exceptional durability against mechanical fatigue and stability at elevated temperature and humidity meet the prerequisite for future soft biomedical robots that enable long‐lasting safe operations.
Electrical neural interfaces provide direct communication pathways between living brain tissue and engineered devices to understand brain function. However, conventional neural probes have remained limited in providing stable, long-lasting recordings because of large mechanical and structural mismatches with respect to brain tissue. The development of flexible probes provides a promising approach to tackle these challenges. In this review, various structural designs of flexible intracortical probes for promoting long-term neural integration, including thin film filament and mesh probe structures that provide similar geometric and mechanical properties to brain tissue and self-deployable probe structure that enables moving the functional sensors away from the insertion trauma, are summarized, highlighting the important role of structural design in improving the long-term recording stability of neural probes.
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