Michael C. McAlpine’s research while affiliated with University of Minnesota, Duluth and other places

What is this page?


This page lists works of an author who doesn't have a ResearchGate profile or hasn't added the works to their profile yet. It is automatically generated from public (personal) data to further our legitimate goal of comprehensive and accurate scientific recordkeeping. If you are this author and want this page removed, please let us know.

Publications (99)


Aspiration‐assisted printing strategy for a single static organism. A) Schematic of the printing strategy. This strategy was developed using a testbed of zebrafish embryos. Characterization of the picking process for embryos: B) determination of optimal vacuum pressure (left, n = 15) based on the deformation of the chorions of the embryos (right) as shown by the dotted rectangle, C) embryo picked up by a nozzle under an optimal vacuum pressure of 2.5 kPa (left) and its observation after being separated from the nozzle (right), D) finite element (FE)‐predicted stress distribution of a chorion of an embryo during picking, and E) survival rates of embryos 3 d after the picking process (t1 = 0.5 s, t2 = 1 s, t3 = 2 s, and t4 = 3 s) (n = 30). Characterization of the placing process for embryos: F) determination of the nozzle distance from the substrate (left, n = 9), based on the critical burst distance as defined by the distance in which the blastoderm and yolk underwent structural damage due to compression by the nozzle (right), G) embryo placed with an optimal nozzle distance of 800 µm, and H) FE‐predicted stress distribution of the chorions of embryos during placing. I) Survival rates (n = 100) and J) images of embryos after the picking and placing processes. K) Embryos placed on circular target marks. The embryos were highlighted with dotted circles to assist in their visualization. The images in B), C) (right), and J) are optical microscope images, and the remainder of the images are photographs.
Aspiration‐assisted printing strategy for multiple organisms. A) Schematic of the printing strategy. This strategy was developed with testbeds of dinoflagellates, shrimp embryos, and shrimp larvae. B) Printing dinoflagellates in seawater droplets. i) Graph (n = 5) and ii) images (mesh‐filtered nozzle diameter (ND): 1200 µm) showing the effect of vacuum times (VTs) on the number of dinoflagellates picked at the end of a mesh‐filtered nozzle. iii) Graph (n = 5) and iv) images (left and center, mesh‐filtered ND: 1200 µm) showing the effect of dispensing times (DTs) on the volumes of placed dinoflagellate‐laden droplets. The rightmost image in (iv) shows a single dinoflagellate taken from the droplet. C) Survival rates of printed dinoflagellates (n = 15). D) Printing shrimp embryos in ≤ 1 µL droplets with different viscosities. i) Graph (n = 5) and ii) images (10% PEG) showing the effect of the VTs on the number of embryos picked at the end of the mesh‐filtered nozzle. iii) Graph (n = 5) showing the effect of the VTs on the volume of placed embryo–laden droplets. iv) Images showing an embryo–laden droplet (left, 10% PEG) and a single embryo taken from the droplet (right). E) Survival rates of printed shrimp embryos (n = 15). F) Printing shrimp larvae in ≤ 1 µL droplets with different viscosities. i) Graph (n = 5) and ii) images (10% PEG) showing the effect of the mesh‐filtered NDs on the number of picked larvae. iii) Graph (n = 5) showing the effect of the mesh‐filtered NDs on the volumes of placed larva–laden droplets. iv) Images showing a larva–laden droplet (left, 10% PEG) and a single larva taken from the droplet (right). G) Survival rates of printed shrimp larvae (n = 10). Each solution was tested with different NDs indicated by the fill patterns of the bar charts. The rightmost images in (B) iv), D) iv), and F) iv) are optical microscope images, while the remainder of the images are photographs.
Aspiration‐assisted printing strategy for a single moving organism. A) Schematic of the printing strategy. This strategy was realized with a testbed of beetles. Characterization of the picking process for beetles: B) determination of the vacuum pressure (n = 5) and C) tracking errors of the adaptive printing system (MVS: machine vision system and PS: printing system) (n = 5). Characterization of the placing process for beetles: D) trajectories of the beetles in different Pluronic hydrogel thicknesses. E) Survival rates of the beetles after printing and removing Pluronic hydrogel (n = 30). F) Beetles tracked and picked up by a white‐covered nozzle: i) a randomly moving beetle on a transparent substrate, ii) a nozzle tracking the beetle (left) based on its spatial location as detected by the machine vision system (right), and iii) a beetle picked up by a nozzle (left) when it meets pre‐programmed criteria (right). G) Beetles placed in Pluronic hydrogel by a white‐covered nozzle: i) a beetle escaping from a thin hydrogel structure, ii) a beetle placed in a thick hydrogel structure, iii) an array of beetles created via immobilization in thick hydrogel structures, iv) beetles placed along with a target arrow direction in a hydrogel bath, and v) a beetle tower created with hydrogel on a target circle. The target circle, which is covered by the beetles, can be observed in Movie S4 (Supporting Information). The images in F and G are photographs.
Applications of aspiration‐assisted printing of organisms. A) Zebrafish embryo‐included cryoprotectant droplets: i) embryos with different cryoprotectant droplets placed on cryotop devices at random locations and heights, and ii) cryopreservation and laser rewarming of gold nanorod (GNR)‐injected embryos with GNR‐included cryoprotectant droplets. B) Shrimp embryo–laden cryoprotectant droplets: i) embryos with cryoprotectant droplets placed on cryotop devices at random locations and heights, and ii) their cryopreservation and convective rewarming. C) Sorting and conformal placing of live zebrafish embryos: i) the process of sorting live embryos from dead embryos and microspheres, and ii) placing live embryos on a curved copper surface. The inset in (i) shows an example of picking up a microsphere via aspiration‐assisted printing. D) Dinoflagellate‐based displays: i) printing dinoflagellates into silicone chambers that were conformally printed on a spherical surface, ii) spherical display attached to a speaker for testing, iii) spherical display emitting bioluminescence in response to audio‐induced vibrations, iv) planar display attached to a speaker for testing, v) planar display displaying the letters “GO” in response to audio‐induced vibrations. E) Beetles with integrated secret symbols and electronic devices: i) printing UV‐responsive secret symbols (3 layers) on a beetle placed in a hydrogel structure, ii) beetles displaying secret symbols (triangle, square, and circle) under UV light, and their scale relative to a fingertip, iii) beetle with integrated electrodes and light‐emitting diode (LED), and its scale relative to a fingertip, and iv) multiple beetles with integrated electrodes and LEDs in a hydrogel bath. All images are photographs.
3D Printed Organisms Enabled by Aspiration‐Assisted Adaptive Strategies
  • Article
  • Full-text available

June 2024

·

74 Reads

·

1 Citation

Guebum Han

·

Kanav Khosla

·

Kieran T. Smith

·

[...]

·

Michael C. McAlpine

Devising an approach to deterministically position organisms can impact various fields such as bioimaging, cybernetics, cryopreservation, and organism‐integrated devices. This requires continuously assessing the locations of randomly distributed organisms to collect and transfer them to target spaces without harm. Here, an aspiration‐assisted adaptive printing system is developed that tracks, harvests, and relocates living and moving organisms on target spaces via a pick‐and‐place mechanism that continuously adapts to updated visual and spatial information about the organisms and target spaces. These adaptive printing strategies successfully positioned a single static organism, multiple organisms in droplets, and a single moving organism on target spaces. Their capabilities are exemplified by printing vitrification‐ready organisms in cryoprotectant droplets, sorting live organisms from dead ones, positioning organisms on curved surfaces, organizing organism‐powered displays, and integrating organisms with materials and devices in customizable shapes. These printing strategies can ultimately lead to autonomous biomanufacturing methods to evaluate and assemble organisms for a variety of single and multi‐organism‐based applications.

Download

3D Printed Microfluidics: Advances in Strategies, Integration, and Applications

February 2023

·

157 Reads

·

83 Citations

Lab on a Chip

The ability to construct multiplexed micro-systems for fluid regulation could substantially impact multiple fields, including chemistry, biology, biomedicine, tissue engineering, and soft robotics, among others. 3D printing is gaining traction as a compelling approach to fabricating microfluidic devices by providing unique capabilities, such as 1) rapid design iteration and prototyping, 2) the potential for automated manufacturing and alignment, 3) the incorporation of numerous classes of materials within a single platform, and 4) the integration of 3D microstructures with prefabricated devices, sensing arrays, and nonplanar substrates. However, to widely deploy 3D printed microfluidics at research and commercial scales, critical issues related to printing factors, device integration strategies, and incorporation of multiple functionalities require further development and optimization. In this review, we summarize important figures of merit of 3D printed microfluidics and inspect recent progress in the field, including ink properties, structural resolutions, and hierarchical levels of integration with functional platforms. Particularly, we highlight advances in microfluidic devices printed with thermosetting elastomers, printing methodologies with enhanced degrees of automation and resolution, and the direct printing of microfluidics on various 3D surfaces. The substantial progress in the performance and multifunctionality of 3D printed microfluidics suggests a rapidly approaching era in which these versatile devices could be untethered from microfabrication facilities and created on demand by users in arbitrary settings with minimal prior training.



A Bionic Testbed for Cardiac Ablation Tools

November 2022

·

49 Reads

·

3 Citations

Bionic-engineered tissues have been proposed for testing the performance of cardiovascular medical devices and predicting clinical outcomes ex vivo. Progress has been made in the development of compliant electronics that are capable of monitoring treatment parameters and being coupled to engineered tissues; however, the scale of most engineered tissues is too small to accommodate the size of clinical-grade medical devices. Here, we show substantial progress toward bionic tissues for evaluating cardiac ablation tools by generating a centimeter-scale human cardiac disk and coupling it to a hydrogel-based soft-pressure sensor. The cardiac tissue with contiguous electromechanical function was made possible by our recently established method to 3D bioprint human pluripotent stem cells in an extracellular matrix-based bioink that allows for in situ cell expansion prior to cardiac differentiation. The pressure sensor described here utilized electrical impedance tomography to enable the real-time spatiotemporal mapping of pressure distribution. A cryoablation tip catheter was applied to the composite bionic tissues with varied pressure. We found a close correlation between the cell response to ablation and the applied pressure. Under some conditions, cardiomyocytes could survive in the ablated region with more rounded morphology compared to the unablated controls, and connectivity was disrupted. This is the first known functional characterization of living human cardiomyocytes following an ablation procedure that suggests several mechanisms by which arrhythmia might redevelop following an ablation. Thus, bionic-engineered testbeds of this type can be indicators of tissue health and function and provide unique insight into human cell responses to ablative interventions.


Skin‐interfaced photodetector system for in‐situ light intensity monitoring. A) Schematic illustration of the photodetector array with a console in operation. The system consists of a photodetector array for monitoring the light intensity of eight different wavelengths and a custom‐built console for signal processing and wireless data transmission. B) Schematic of the 3D printed photodetector array. The photodetectors and optical filters with eight different central wavelengths are assembled on the top and backside of the flexible polydimethylsiloxane (PDMS) substrate, respectively. The left inset is an exploded view of one photodetector with an optical bandpass filter. The right inset is the positioning of the central wavelengths of the optical bandpass filters. C) Schematic of the console for the monitoring system. The console consists of a custom‐built signal processing board for driving photodetectors and processing photocurrent signals, a single‐board processor for data processing and transmission, and an uninterruptable power supply (UPS) module for power management. D) Schematic block diagram of the monitoring system.
Characterization of the hybrid active materials and 3D printing of the photodetector. A) Atomic force microscopy (AFM) images of active films with 0ZnO (i), 1ZnO (ii), 2ZnO (iii), and 3ZnO (iv). B) Root mean square (RMS) roughness of films printed with the active materials (n = 5). C) Normalized transmission spectra of active films. The insets are optical microscope images of active films. The scale bars are 50 µm. D) The dependence of contact angle on UV ozone treatment time (n = 5). The insets are images of droplets on the PDMS film. The scale bars are 1 mm. E) Images of printing steps of one photodetector. The scale bar is 5 mm. In B) and D), data are presented as mean ± SD.
Characterization of photoresponse of printed photodetectors. A‐C) Sensitivity of photodetectors with varying active materials at a bias voltage of −1 V and wavelengths of A) 310 nm, B) 360 nm, and C) 520 nm, respectively (n = 3). The insets are current‐intensity characteristics of PD2. D‐F) Responsivity, external quantum efficiencies (EQE), and detectivity, respectively, at a bias voltage of ‐1 V of the photodetectors printed with the various active materials (n = 3). Data are presented as mean ± SD.
Stability and stretchability of the 3D printed photodetectors. A–C) Current response of a photodetector to 310 nm, 360 nm, and 520 nm on/off modulated light, respectively, in the last 8 h of a test period of 14 h. The light intensities used in A–C) are ≈4.6, 9.2, and 21.1 µW cm–2, respectively. The insets are magnified views of current responses. D) Bending test of the photodetector (n = 5). The left and right insets are the photodetectors undergoing curvatures of 0.46 and 1.37 cm–1, respectively. The scale bars are 10 mm. E) Photocurrent and dark current of the photodetector at varying tensile strains (n = 5). F) Images showing a photodetector under 0% (i) and 29.3% (ii) strain, respectively. The scale bars are 10 mm. (iii) and (iv) are optical microscope images of the sensing areas in (i) and (ii), respectively. The scale bars are 1 mm. In D) and E), data are presented as mean ± SD.
3D printed skin‐interfaced light intensity monitoring system. A) Image of the photodetector array for monitoring the light intensity of eight different wavelengths. B) Image of the console containing a signal processing board, a single‐board processor, and a UPS module. The console is connected to the 3D printed photodetector array via a flat flexible cable (FFC). The scale bars in figure A and B are 10mm. C) Image of the wearable photodetector system attached to a hand for in‐situ light intensity monitoring. D) The light intensity, measured by the monitoring system, of eight different wavelengths ranging from UVB to the visible band of natural sunlight during a full day in Minneapolis, Minnesota, on May 12, 2021.
3D Printed Skin‐Interfaced UV‐Visible Hybrid Photodetectors

July 2022

·

151 Reads

·

21 Citations

Photodetectors that are intimately interfaced with human skin and measure real‐time optical irradiance are appealing in the medical profiling of photosensitive diseases. Developing compliant devices for this purpose requires the fabrication of photodetectors with ultraviolet (UV)‐enhanced broadband photoresponse and high mechanical flexibility, to ensure precise irradiance measurements across the spectral band critical to dermatological health when directly applied onto curved skin surfaces. Here, a fully 3D printed flexible UV‐visible photodetector array is reported that incorporates a hybrid organic‐inorganic material system and is integrated with a custom‐built portable console to continuously monitor broadband irradiance in‐situ. The active materials are formulated by doping polymeric photoactive materials with zinc oxide nanoparticles in order to improve the UV photoresponse and trigger a photomultiplication (PM) effect. The ability of a stand‐alone skin‐interfaced light intensity monitoring system to detect natural irradiance within the wavelength range of 310–650 nm for nearly 24 h is demonstrated.


Fig. 1. Schematic of the fully 3D-printed OLED display and printing methodology. (A) Exploded view of the OLED display demonstrating its layer-by-layer structure. Layers 1 through 6 are 3D-printed components. The OLED display was printed on PET films that were mounted with electrical connection pins and encapsulated with PDMS. (B) Schematic demonstrating the methods for printing and reconfiguring each component of the OLED display. (C) Energy band diagram of the OLED showing the transport and recombination of the charge carriers under a constant or pulsed external voltage. From left to right, the four materials are AgNPs, PEDOT:PSS, MDMO-PPV, and EGaIn. The inset image displays the molecular structure of MDMO-PPV. hv, absorbed photons. (D) Electroluminescence (EL) spectrum of the 3D-printed OLED. a.u., arbitrary units.
Fig. 2. Spray printing of MDMO-PPV as the active layer of the OLEDs for improved layer uniformity and device performance. (A) Optical images of MDMO-PPV layers on the macro and micro scales. Circular layers in the top and bottom rows were deposited by spray and extrusion printing, respectively. Photo credit: Sung Hyun Park, University of Minnesota. (B) Surface profiles of two MDMO-PPV layers that were spray-and extrusion-printed. Ink concentrations of 1 and 8 mg/ml were used for extrusion and spray printing, respectively. (C) Plot of the relationship between the mean thicknesses of MDMO-PPV layers and spray times under two different concentrations. The thicknesses were linearly fitted. n = 5. The inset image shows the spray-printed active layer with an ink concentration of 8 mg/ml. Photo credit: Sung Hyun Park, University of Minnesota. (D) Optical images of spray-printed MDMO-PPV LEDs under operation. Devices in each row had the same spray-printed thickness, and devices in each column were operated under the same voltage. Photo credit: Sung Hyun Park, University of Minnesota. (E) I-V curves of spray-printed MDMO-PPV LEDs that have active layers with different thicknesses. The inset plot magnifies the I-V curves of 320 and 400 nm in the range of 1 to 3 V with the same axis titles and units as the main plot. (F) Plot of the relationship between the irradiance and operation time for spray-and extrusion-printed MDMO-PPV LEDs that were injected with a current of 30 A. The two tested devices have a similar mean active layer thickness of ca. 300 nm.
Fig. 3. Mechanical reconfiguration of printed EGaIn droplets. (A) Schematic of morphology variation of one EGaIn droplet during mechanical reconfiguration with a tapered polypropylene nozzle mounted on the 3D printer. The inset images show the bottom views of one EGaIn droplet before and after reconfiguration. Photo credit: Ruitao Su, University of Minnesota. (B) Schematic h-t curve depicting the motion of the nozzle during EGaIn reconfiguration. The inset images show the side views of one EGaIn droplet during different stages of the reconfiguration. Photo credit: Ruitao Su, University of Minnesota. (C) Compression force versus time curve demonstrating an increasing trend with discontinuities for the force applied to the EGaIn droplet as the nozzle moved downward. (D) Illustration of the formation of new oxide surfaces during surface ruptures. (E) SEM micrographs demonstrating features on the surface of EGaIn droplets after reconfiguration. (I) Image at lower magnification showing the coexistence of several features. (II) A zoom-in view of the boundaries between the original and new oxide surfaces created by the surface ruptures. (III) A zoom-in view of folds of the oxide surface formed during the retraction of the nozzle. (IV) A zoom-in view of the wrinkles formed on the oxide surface during surface relaxation. Image credit: Ruitao Su, University of Minnesota. (F) Complete force-time curves demonstrating the four stages during reconfiguration and the high repeatability of this process for a wide range of compression rates. (G) Plots of variations of the morphological metrics, including junction contacting area and height of EGaIn droplets, before and after reconfiguration for compression rates spanning three orders of magnitude. n = 5. (H) Plot of the relationship between the ratio of morphological metrics after and before reconfiguration and varying compression depths. n = 5.
Fig. 4. Printing top interconnects and characterization of the 3D-printed OLED display. (A) (I) Cross-sectional illustration of two interconnected OLEDs in the display with the top interconnects conformally printed over the reconfigured EGaIn cathodes. (II) Side view of one row in the OLED display before PDMS encapsulation was applied. Photo credit: Ruitao Su, University of Minnesota. (B) (I) Images of a completed OLED display, the light emission of which was viewed from the backside. (II) Schematic circuit and driving mechanism of the OLED display. Photo credit: Ruitao Su, University of Minnesota. (C) Image of the word "HELLO" while the text scrolled on the 8 × 8 OLED display. Photo credit: Ruitao Su, University of Minnesota. (D) Transient characteristics of the 3D-printed OLED and a commercial AlGaInP-based LED. (E) Histogram plot showing the irradiance distribution of the 64 pixels in the LED display when each pixel was injected with a current of 10 mA.
Fig. 5. Bending characterization of the 3D-printed flexible OLED display. (A) Four different combinations of bending orientations for the OLED display during the bending test. Photo credit: Ruitao Su, University of Minnesota. (B and C) Optical power of the 3D-printed OLEDs as the bending curvature increased for the four different bending combinations. n = 5. (D) Images of the OLED display in flat and bent states while mounted on the testing stage. Photo credit: Ruitao Su, University of Minnesota. The tested row of LEDs was under the largest curvature and operated with a current of 10 mA. (E) Images of the bent OLED device array while a pattern was displayed on it. (I and II) The backside of the display was bent outward. (III and IV) The backside of the display was bent inward. Photo credit: Ruitao Su, University of Minnesota.
3D-printed flexible organic light-emitting diode displays

January 2022

·

967 Reads

·

96 Citations

Science Advances

The ability to fully 3D-print active electronic and optoelectronic devices will enable unique device form factors via strategies untethered from conventional microfabrication facilities. Currently, the performance of 3D-printed optoelectronics can suffer from nonuniformities in the solution-deposited active layers and unstable polymer-metal junctions. Here, we demonstrate a multimodal printing methodology that results in fully 3D-printed flexible organic light-emitting diode displays. The electrodes, interconnects, insulation, and encapsulation are all extrusion-printed, while the active layers are spray-printed. Spray printing leads to improved layer uniformity via suppression of directional mass transport in the printed droplets. By exploiting the viscoelastic oxide surface of the printed cathode droplets, a mechanical reconfiguration process is achieved to increase the contact area of the polymer-metal junctions. The uniform cathode array is intimately interfaced with the top interconnects. This hybrid approach creates a fully 3D-printed flexible 8 × 8 display with all pixels turning on successfully.



3D extrusion bioprinting

November 2021

·

988 Reads

·

213 Citations

Nature Reviews Methods Primers

Three-dimensional (3D) bioprinting strategies use computer-aided processes to enable automated simultaneous spatial patterning of cells and/or biomaterials. These technologies are suitable for a broad range of biomedical applications owing to their capability to produce structurally sophisticated and functionally relevant tissue constructs. Extrusion-based 3D bioprinting strategies were among the first modalities developed and are now arguably the most widely used for producing 3D tissue constructs. These technologies have rapidly evolved over the past two decades, providing a powerful tool set for the biofabrication of tissues that can facilitate translational efforts in the field. In this Primer, we describe the methodology of 3D extrusion bioprinting, focusing on the selection of hardware, software and bioinks. We expand upon recent advances in 3D extrusion bioprinting by illustrating the key variations that promote its biofabrication abilities. Finally, we provide an outlook on possible future refinements of the technology. 3D extrusion bioprinting methods can be used to produce tissue constructs in vitro and in situ and are arguably the most commonly used bioprinting strategies. In this Primer, Zhang and colleagues describe the variants of 3D extrusion bioprinting methods and their specific applications, considerations for the formulation of bioinks and strategies for assessing print quality. The authors conclude by looking to recent and upcoming developments in 4D printing and artificial intelligence-assisted dynamic printing strategies.




Citations (74)


... This technique enables picking and placement of biologics ranging from 80 to 800 μm in size into or onto a gel substrate with minimal cellular damage ( > 90% cell viability) and achieving high positional precision (~11% with respect to spheroid size). AAB has recently inspired applicability in magnetic lifting of neural organoids for the construction of assembloids 15 , 3D printing of living moving organisms (i.e., beetles 18 ) and bioprinting of high cell-density tissues (i.e., cartilage 19 and bone 20 ) and disease models (post-myocardial infarction scarring) 3 . However, the major limitation of this technique is its reliance on bioprinting one spheroid at a time. ...

Reference:

High-throughput bioprinting of spheroids for scalable tissue fabrication
3D Printed Organisms Enabled by Aspiration‐Assisted Adaptive Strategies

... One of the main advantages of microfluidic technology is its ability to integrate multiple laboratory functions onto a single chip, thereby reducing the required sample volumes, shortening analysis times, and lowering reagent consumption [3,4]. This miniaturization not only enhances the efficiency of analytical processes but also opens up new possibilities for point-of-care testing and personalized medicine [3,5,6]. ...

3D Printed Microfluidics: Advances in Strategies, Integration, and Applications
  • Citing Article
  • February 2023

Lab on a Chip

... Gelatin methacryloyl (GelMA) is one of the most common base components of bioinks used in scaffold fabrication and bioprinting, including the ISED approach, 6,[10][11][12]14,16 as its natural and synthetic components allow for tunable properties, cell binding motifs, and printability. 18 Tunable properties include matrix stiffness and pore size, altered by the source of raw gelatin, degree of gelatin functionalization (DoF), and GelMA concentration in the bioink. ...

A Bionic Testbed for Cardiac Ablation Tools

... Over the last decade, the formulation of colloidal nanoparticle inks for the development of highperformance flexible printed electronics has garnered attention within the scientific community [1][2][3]. Also, the use of nano-inks in the manufacture of lowpowered printed electronics in the biomedical sector, automotive industries and fabrication of components for solar-energy harnessing has improved drastically [4]. Although the techniques utilizing metal oxide-based nanoparticle inks have been commercialized, there is still scope to explore the potential opportunities in printed electronics for fabricating internet-of-things (IoT) technologies such as radiofrequency identification tags, chemiresistive smart gas sensors and thin-film transistors [5][6][7]. ...

The 2021 flexible and printed electronics roadmap

... Similarly, ZnO nanoparticles incorporated into polymeric photoactive materials were used to 3D print a flexible photodetector which could be interfaced to human skin to measure spectral irradiance over a specified time period. 254 A 24 h detection of wavelengths in the region of 310-650 nm, corresponding to natural light irradiance, was demonstrated to be possible with these flexible and wearable sensors. These types of new and emerging manufacturing techniques, give a glimpse into the future of photodetector devices and the critical role that ZnO plays in their operation, given its ubiquitous position as a robust and inexpensive semiconductor with a wide bandgap. ...

3D Printed Skin‐Interfaced UV‐Visible Hybrid Photodetectors

... Thanks to the possibility of creating any type of geometry which would otherwise be difficult to produce in a reasonable time and at a low cost, 3D printing finds application in many fields, including industry [23], architecture [24], agriculture [25], dentistry [26], aerospace [27], medical research [28], and various fields of engineering, including microfluidic engineering. ...

3D-printed flexible organic light-emitting diode displays

Science Advances

... The first successful protocol for zebrafish embryo vitrification employed a cryotop-like device made with a polypropylene strip. [58][59][60] However, such a protocol can vitrify one zebrafish embryo on cryo-top at a time, considerably limiting the throughput of cryopreservation. With the previous protocol, a well-trained operator can only vitrify 10-15 embryos in an hour. ...

Ultra Rapid Laser Warming For Preservation of Fish and Other Aquatic Species
  • Citing Article
  • December 2021

Cryobiology

... While organoids and spheroids often suffer from batch-to-batch variability [19], bioprinted models, in contrast, offer consistency in production, making them favorable for reproducible higher-throughput drug screening [20]. Among these technologies, extrusion and digital light processing (DLP)-based bioprinting methods have gained significant attentions [21][22][23]. DLP, in particular, stands out for its high resolution and speed, which enable the fabrication of detailed, biomimetic structures [24,25]. Different from extrusion-based bioprinting, which plots materials to form constructs in a point-by-point manner, DLP uses light to solidify bioinks directly layer-by-layer, resulting in smoother, more accurate models in many scenarios [26,27]. ...

3D extrusion bioprinting
  • Citing Article
  • November 2021

Nature Reviews Methods Primers

... (C) Capillary microfluidic encapsulation of a biosample in core-shell microcapsules. Reproduced with permission from Wiley, 2021 [118]. (D) Cryobioprinting of tissue constructs for simultaneous cryopreservation. ...

Conduction Cooling and Plasmonic Heating Dramatically Increase Droplet Vitrification Volumes for Cell Cryopreservation

... The preservation of the optical properties was the focus due to its direct impact on the thermal performance of the solution. The extinction coefficient of TiN NPs, TiN clusters, and GNRs was evaluated by suspending the nanomaterials in 15% methanol (MeOH), 7.5% propylene glycol (PG), and 20% polyethylene glycol (PEG), a CPA solution developed by Smith et al. (2020) to successfully vitrify a biomaterial microdroplet. Solutions of 5 mL CPAs with concentrations as high as 100 μg/ mL of each nanomaterial were sonicated for 6 min to obtain homogenized samples. ...

High throughput cryopreservation of aquaculture seed
  • Citing Article
  • December 2020

Cryobiology