Yuval Elani’s research while affiliated with Imperial College London and other places

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Publications (92)


On-the-Fly Microfluidic Control of Giant Vesicle Compositions Validated by DNA Surface Charge Sensors
  • Article

April 2025

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5 Reads

ACS Nano

Marcus Fletcher

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Yuval Elani

Overview of the dynamic behaviors for thermally responsive PEO‐PBO polymersomes and droplets. The dynamic behaviors are split into responses on the nanoscale (purple shading) and microscale (blue shading). On the nanoscale, the polymersomes can be utilized for cargo release (A), behave as thermosensitive organelles (B), and generate microsized sponge‐like droplets (C). Meanwhile, on the microscale, the polymeric structures exhibit thermoresponsive contractility (D), fusion between droplets (E), and material capture (F).
The temperature response of the PEO‐PBO polymer. A) A schematic of the chemical composition of the PEO‐PBO polymer. The hydrophobic PBO polymer is shown as the orange coiled chain of the PEO‐PBO polymer while the hydrophilic PEO polymer is shown as the blue chain. B) A Transmission electron microscopy image of the PEO‐PBO polymer, limited structural order can be seen which is consistent with sponge phases. The scale bar is 50 nm. C) A schematic showing the sponge phase of the PEO‐PBO polymer. D) A SAXS plot demonstrating how a heating/cooling cycle alters the phase behavior of the PEO‐PBO polymer. The heating and cooling portions of the graph are indicated by the thermometer schematics. Enlarged regions highlight the phases of the polymer with diagrams at the beginning, middle, and end of the cycle. Above 60 °C, an inverse hexagonal (HII) phase is present which disappears upon cooling. E) A ¹H NMR plot showing how the chemical shift of the PEO‐PBO polymer alters during a heating/cooling cycle. The heating and cooling portions are indicated by the thermometer schematics in the graph. Upon heating, a shift to higher ppm is seen. Upon cooling, the signal shifts back to a lower ppm but does not fully return to the original position before the temperature cycle. F) A schematic illustrating the change in packing and curvature of the polymer during heating and cooling. Heating to 70 °C causes dehydration of the copolymer's hydrophilic block (shown by the color change), resulting in increased curvature and structural rearrangements. Cooling reverses the conformational changes, restoring the polymer's original packing and structure's curvature.
Temperature responsive behavior of PEO‐PBO polymersomes. A) Schematic showing the extrusion method for making small unilamellar vesicles (SUVs) from self‐assembled larger vesicles. B) A Cryo‐TEM micrograph of PEO‐PBO polymersomes at 25 °C. The scale bar is 100 nm. C) DLS size scans with attached autocorrelation functions showing how the polymersome size changes with temperature. From 60 °C onwards, the polymersome size starts to increase. D) A size versus temperature plot illustrating the impact of heating/ cooling cycles on the size and polydispersity (PDI) of PEO‐PBO polymersomes. Repeated cycles result in an increase in both size and polydispersity attributed to polymersome fusion. The shaded region of the plot indicates where the temperature remained constant at 60 °C. E) A schematic indicating the change in size of the polymersome structures as they undergo the heating/cooling cycles. F) Representative Cryo‐TEM micrographs of PEO‐PBO polymersomes heated to 40, 50, and 65 °C. At 40 and 50 °C, polymersomes were similar in size, though, at 65 °C, substantially larger polymersomes are present through the fusion of the polymersomes. The scale bars are 200 nm. G) A graph showing the release kinetics of calcein from PEO‐PBO polymersomes at 25 and 65 °C and lipid DOPC and DPPC vesicles at 25 and 65 °C. H) A bar chart comparing the temperature of calcein release from PEO‐PBO polymersomes to DOPC and DPPC vesicles. An increase in normalized fluorescence corresponds to the release of calcein from the vesicles or polymersomes. Both DPPC and PEO‐PBO show a release of calcein at their transition temperatures.
Utilizing fusogenic PEO‐PBO polymersomes for synthetic cell construction. A) A schematic illustrating that through using a temperature ramp of 5 °C a minute to 70 °C, a 5‐minute incubation at 70 °C, and cooling back to room temperature the PEO‐PBO polymersomes assemble into larger polymeric droplet structures. B) Fluorescence and brightfield images of a population of spherical polymeric droplets stained with Nile Red. The fluorescence is localized to the droplets. The scale bars are 25 µm. C) A confocal fluorescence 3D Z‐stack showing half of a polymeric droplet. The fluorescence signal originates from a lipophilic rhodamine dye incorporated within the PEO‐PBO bilayer. The accompanying schematic highlights the spongelike phase and polymer bilayer structure of the polymeric droplets. Scale bar is 10 µm. D) A histogram with a Kernal density estimation fit showing the mean diameter of a population of polymeric droplets was 17 µm with a polydispersity index of 0.24. n = 100 polymeric droplets were measured. E) Laurdan assay (excitation = 360 nm) reveals a red shift in the fluorescence spectrum upon heating, indicating Laurdan gains easier access to water molecules at elevated temperatures. Upon cooling back to 25 °C, the spectrum shifts blue again, suggesting the reformation of a membrane‐based structure in the droplets during the process. F) A fluorescence recovery after photobleaching graph with embedded confocal microscopy images showing the recovery of fluorescence within a polymeric droplet, indicating the droplet is comprised of a fluid polymeric membrane structure. The scale bars are 10 µm. G) Calcein permeation of polymeric droplets. A fluorescence image and corresponding line profile taken 60 min after the addition of 0.5 µm calcein to the polymeric droplet solution shows darker regions in the fluorescence corresponding to the positions of the droplets. These dark areas indicate limited calcein permeation into the sponge droplet interior, demonstrating that the polymeric membrane effectively separates the internal and external aqueous solutions successfully. The dashed line shows the line profile taken for the plot The scale bar is 50 µm. H) Brightfield images demonstrating a formation timelapse of larger PEO‐PBO aggregates within lipid vesicles upon heating. The scale bars are 25 µm.
Functionality and applications of contractile PEO‐PBO polymeric droplets. A) An illustration indicating the reversible contractility observed within PEO‐PBO polymeric droplets. The dotted circle shows the relative size of the polymer droplet before and after the contraction. The schematic also highlights the reversible decrease in bilayer distance upon heating due to the expulsion of water, leading to a size decrease. B) Brightfield images showing the contractility of PEO‐PBO polymer droplets, upon heating to 70 °C the droplets significantly shrink, this is reversed upon cooling back to 25 °C. The scale bar is 10 µm. C) A plot demonstrating how the size of PEO‐PBO polymeric droplets alters with temperature, a significant shrinkage is seen between 50 and 60 °C. The error bars were obtained from the standard deviation of n = 3 PEO‐PBO polymeric droplets. D) Schematic illustrating the fusion of semi‐contracted PEO‐PBO polymeric droplets at an elevated temperature before the formation of a larger uncontracted droplet upon cooling. During the fusion event, the different polymeric bilayers fuse together. E) Brightfield images showing the timelapse of a fusion event between two semi‐contracted PEO‐PBO polymeric droplets at 55 °C. The scale bar is 20 µm. F) Brightfield images presenting the formation of a singular PEO‐PBO polymeric droplet created from the two fused semi‐contracted polymeric droplets upon cooling. The scale bar is 20 µm. G) An overlapped fluorescence and brightfield microscope image showing the successful encapsulation of calcein. The green color indicates the calcein channel while the plot shows the relative calcein fluorescence change along the black dashed line. Scale bar is 20 µm. H) Drawings with accompanying fluorescence images showing how PEO‐PBO polymersomes can interact with bacteria, with multiple heating/cooling cycles the bacteria are taken up into the produced polymer droplet structure. The scale bars are 10 µm. I) Fluorescence population images of GFP‐expressing bacteria before and after trapping in polymeric droplets. Prior to the heating and cooling cycles, the bacteria are present throughout the sample, while after, the bacteria are localized within the produced polymer droplets. The scale bars are 20 µm.
Thermally Driven Dynamic Behaviors in Polymeric Vesicles
  • Article
  • Full-text available

March 2025

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15 Reads

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Yeyang Sun

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Chi Long Chan

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[...]

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Stimuli‐responsive polymeric vesicles offer a versatile platform for mimicking dynamic cell‐like behaviors for synthetic cell applications. In this study, thermally responsive polymeric droplets derived from poly(ethylene oxide)‐poly(butylene oxide) (PEO‐PBO) polymersomes, aiming to create synthetic cell models that mimic key biological functions are developed. Upon heating, the nanoscale vesicles undergo fusion, transforming into sponge‐like microscale droplets enriched with membrane features. By modulating the temperature, these droplets display dynamic properties such as contractility, temperature‐induced fusion, and cargo trapping, including small molecules and bacteria, thereby demonstrating their ability to dynamically interface with biological entities. The findings demonstrate the potential of our sponge‐like droplets in synthetic cell applications, contributing to the understanding of PEO‐PBO polymersomes’ unique characteristics, expanding the capabilities of synthetic cell structures, and representing an exciting possibility for advancing soft matter engineering to cell‐like behaviors.

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Assembly of two compartment microgels. A) An illustration demonstrating the production of two compartment microgels in a microfluidic device. Two different aqueous streams containing alginate meet and co‐flow until they meet an oil stream containing acetic acid at a flow focusing junction. This generates aqueous droplets with a compartment composition determined by the relative flow rates of the co‐flowing aqueous phases in the oil phase. The droplets are then gelated in flow by the surrounding acetic acid, and the two compartment microgels are collected upon exiting the device. B) A schematic showing the gelation procedure of the two compartment microgels. The EDTA‐Ca complex in the two compartment droplets dissociates upon a pH change produced by the acetic acid in the oil phase. This enables the free Ca²⁺ to cross‐link the alginate chains and gelate the droplets. The droplets are then resuspended in aqueous buffer where the compartmentalized microgels can be observed. C) Microscopy images and accompanying schematics of the production of two compartment microgels with a variety of compartment sizes. By varying the flow rate ratio between the two alginate containing solutions (with one containing fluorescently labelled alginate), a variety of different sized compartments can be generated in the two compartment microgels. The images show the production of two compartment microgels with a small fluorescent alginate compartment, two equal sized compartments, and a large fluorescent alginate compartment produced from 4 wt% alginate flow rate ratios of 0.19, 0.59, and 0.91, respectively. The microscopy images are generated from a fluorescence image of the rhodamine tagged alginate overlaid on a bright‐field image. The scale bars on the microfluidic images are 50 μm while the scale bars on the hydrogel images are 20 μm. D) Histogram with a kernel density estimation fit (red line) showing the average diameter of a population of two compartment microgels, the mean diameter was 88 μm and the polydispersity index was 0.028. The histogram was obtained from the analysis of n = 100 two compartment microgels. E) Box plots demonstrating how the fluorescence intensity of the microgels increases with a higher fluorescence flow rate ratio. The p values were 1.24×10−30$1.24 \times \left(10\right)^{- 30}$ and 4.64×10−34$4.64 \times \left(10\right)^{- 34}$. F) Box plots showing how the fluorescent compartment size within the microgels increases with a higher fluorescence flow rate ratio. The p values were 1.51×10−17$1.51 \times \left(10\right)^{- 17}$ and 6.22×10−40$6.22 \times \left(10\right)^{- 40}$. n = 75 hydrogels were analyzed for each box plot in panels E and F.
Properties of compartmentalized biomimetic microgels. A) An illustration depicting the production of three compartment microgels in a microfluidic device through the use of three aqueous streams containing alginate. B) Microscopy images and accompanying schematics of the production of three compartment microgels with two different fluorescent compartment sizes. The alteration of the flow rate ratios between the three alginate solutions (with one containing fluorescently labeled alginate) produced the different compartment sizes. The images show the production of three compartment microgels with different sized fluorescent compartments, the compartments are denoted by the dashed lines. The three compartment microgel with the smaller fluorescent compartment was produced from 4 wt% alginate with a fluorescent to non fluorescent flow rate ratio of 0.15 while the other microgel was produced with a flow rate ratio of 0.44. The microscopy images are generated from a fluorescence image of the rhodamine tagged alginate overlaid on a bright‐field image. The scale bars on the microfluidic images are 50 μm while the scale bars on the hydrogel images are 20 μm. C) Histogram with a kernel density estimation fit (blue line) showing the average diameter of a population of three compartment microgels, the mean diameter was 121 μm and the polydispersity index was 0.029. The histogram was obtained from the analysis of n = 100 three compartment microgels. D) Box plots showing how the fluorescence intensity of the three compartment microgels increases with a higher fluorescence flow rate ratio. The p value was 8.17×10−38$8.17 \times \left(10\right)^{- 38}$. E) Box plots illustrating how the fluorescent compartment size within the three compartment microgels increases with a higher fluorescence flow rate ratio. The p value was 2.84×10−29$2.84 \times \left(10\right)^{- 29}$. n = 75 hydrogels were analyzed for each box plot in panels D and E. F) Schematic and embedded microscopy images showing the generation of elongated two compartment microgels on chip, the microscopy images are of elongated water in oil droplets in the microfluidic channels and the exit chamber. The scale bars are 100 μm. G) A diagram with accompanying microscopy images showing a different elongated two compartment microgel. The fluorescence image shows the fluorescent compartment, and the dotted lines denote the hydrogel location in the images. The scale bars are 50 μm. H) Box plots showing the difference in aspect ratios between populations of elongated and spherical microgels. The p value was 1.62×10−37$1.62 \times \left(10\right)^{- 37}$. The populations were generated from analyzing n = 75 hydrogels. I) An illustration showing the formation of two compartment microgels with compartments created from different alginate weight percentages. J) A fluorescent image demonstrating the successful formation of two compartment microgels with different weight percentage compartments. The fluorescent signal is from the higher weight percentage alginate compartment. The scale bar is 50 μm.
Properties of compartmentalized biomimetic microgels. A) An illustration depicting the production of three compartment microgels in a microfluidic device through the use of three aqueous streams containing alginate. B) Microscopy images and accompanying schematics of the production of three compartment microgels with two different fluorescent compartment sizes. The alteration of the flow rate ratios between the three alginate solutions (with one containing fluorescently labeled alginate) produced the different compartment sizes. The images show the production of three compartment microgels with different sized fluorescent compartments, the compartments are denoted by the dashed lines. The three compartment microgel with the smaller fluorescent compartment was produced from 4 wt% alginate with a fluorescent to non fluorescent flow rate ratio of 0.15 while the other microgel was produced with a flow rate ratio of 0.44. The microscopy images are generated from a fluorescence image of the rhodamine tagged alginate overlaid on a bright‐field image. The scale bars on the microfluidic images are 50 μm while the scale bars on the hydrogel images are 20 μm. C) Histogram with a kernel density estimation fit (blue line) showing the average diameter of a population of three compartment microgels, the mean diameter was 121 μm and the polydispersity index was 0.029. The histogram was obtained from the analysis of n = 100 three compartment microgels. D) Box plots showing how the fluorescence intensity of the three compartment microgels increases with a higher fluorescence flow rate ratio. The p value was 8.17×10−38$8.17 \times \left(10\right)^{- 38}$. E) Box plots illustrating how the fluorescent compartment size within the three compartment microgels increases with a higher fluorescence flow rate ratio. The p value was 2.84×10−29$2.84 \times \left(10\right)^{- 29}$. n = 75 hydrogels were analyzed for each box plot in panels D and E. F) Schematic and embedded microscopy images showing the generation of elongated two compartment microgels on chip, the microscopy images are of elongated water in oil droplets in the microfluidic channels and the exit chamber. The scale bars are 100 μm. G) A diagram with accompanying microscopy images showing a different elongated two compartment microgel. The fluorescence image shows the fluorescent compartment, and the dotted lines denote the hydrogel location in the images. The scale bars are 50 μm. H) Box plots showing the difference in aspect ratios between populations of elongated and spherical microgels. The p value was 1.62×10−37$1.62 \times \left(10\right)^{- 37}$. The populations were generated from analyzing n = 75 hydrogels. I) An illustration showing the formation of two compartment microgels with compartments created from different alginate weight percentages. J) A fluorescent image demonstrating the successful formation of two compartment microgels with different weight percentage compartments. The fluorescent signal is from the higher weight percentage alginate compartment. The scale bar is 50 μm.
Organelle incorporation into compartmentalized microgels. A) Schematic showing the generation of two compartment microgels with organelles. Lipid vesicle organelles with different fluorescent dyes are placed into the two different alginate solutions which form the different compartments in the microgels, enabling organelles to be spatially separated within the biomimetic microgels. B) Microscopy images showing the generation of two compartment organelle containing microgels. The microfluidic image shows the fluorescent signals from the two different vesicle organelle populations overlaid on a bright‐field image, coflowing through the microfluidic device while the hydrogel image produced from overlaying the two fluorescent signals shows the separation of the two fluorescent organelle populations within the produced microgel. The microfluidic scale bar is 50 μm, and the hydrogel scale bar image is 20 μm. C) Illustration of the production of three compartment microgels with organelles through the use of three different fluorescent lipid vesicle populations in three different alginate solutions. D) Microscopy images showing the production of three compartment organelle containing microgels. The microfluidic image shows the fluorescent signals three different vesicle organelle populations overlaid on a bright‐field image, coflowing through the microfluidic device while the hydrogel image produced from overlaying the three fluorescent signals shows the separation of the three fluorescent organelle populations within the produced microgel. The microfluidic scale bar is 50 μm, and the hydrogel scale bar image is 20 μm. E) Microscopy image showing the production of three compartment microgels with different embedded organelles. These include lipid vesicles for protein capture, magnetic particles for motility, and lipid vesicles containing a fluorescent dye for controlled release. The fluorescent signal from the controlled release vesicles is overlaid on the bright‐field image to show the coflowing of the different organelle containing phases. The scale bar is 100 μm. F) Schematic with an accompanying microscopy image showing the separated functional organelles in a three‐compartment microgel. The overlaid fluorescent signal is from the fluorescent Calcein dye in the intact controlled release vesicles, and the dotted lines show the compartment boundaries. The scale bar is 20 μm.
Three compartment microgel organelle functionality. A) An illustration of how controlled release is achieved from the vesicle organelles in the three compartment microgels. The addition of the enzyme sPLA2 (the blue partial circle) causes cleavage of lipid tails. This produces defects in the vesicle organelle bilayers causing the release of the entrapped Calcein dye. B) A time lapse graph showing on sPLA2 addition an increase in fluorescent signal is observed due to Calcein release from the vesicle organelles. There is no release without sPLA2 addition. The microscopy images show the fluorescence change between 0 and 600 min around a microgel exposed to sPLA2.The dotted circle shows the hydrogel position. The error bars represent the standard deviations from n = 3 microgel populations. The scale bars are 20 μm. C) A schematic illustrating the motion of the three compartment microgels on magnetic field application. D) Plot showing the movement of three compartment microgels over 10 s with and without magnetic field application. Motion is observed on magnetic field application. The embedded microscopy images show the movement of a microgel before and after magnetic field exposure. The X is the starting position, and the blue line showcases the trajectory taken in the 10 s. The error bars on the graph are the standard deviation of the motion of n = 10 three compartment microgels. The scale bars are 50 μm. E) A diagram showing how protein capture is achieved. On incubation with Streptavidin, the Biotin‐PE lipid (yellow lipid) present on the vesicle organelles will bind Streptavidin, generating a localized fluorescent signal on the organelles. F) Fluorescence images before and after fluorescent Streptavidin addition. On fluorescent Streptavidin addition, a localized fluorescent signal is observed indicating protein capture. The dotted circle shows the position of a hydrogel before Streptavidin addition. The scale bars are 20 μm. G) Box plots demonstrating how the fluorescence of microgels containing Biotin‐PE vesicles increases on fluorescent Streptavidin addition. The p values were 6.40×10−24$6.40 \times \left(10\right)^{- 24}$ and 3.47×10−19$3.47 \times \left(10\right)^{- 19}$. n = 50 hydrogels were analyzed for each condition.
Microfluidic Production of Spatially Structured Biomimetic Microgels as Compartmentalized Artificial Cells

February 2025

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54 Reads

Artificial cells serve as promising micro‐robotic platforms that replicate cellular features. One ubiquitous characteristic of living cells is compartmentalization of content in distinct and well‐defined locations. Herein, a microfluidic strategy to mimic compartmentalization is developed through the production of micron‐scale two and three compartment biomimetic microgels, where hydrogel compartment number, composition, size, and shape can be controlled. Our lab‐on‐chip system enables the incorporation of various synthetic organelles into spatially separated compartments within the microgels. This design concept allows for the introduction of a variety of individually triggered bioinspired behaviors, including protein capture, enzyme‐mediated content release, and stimuli‐triggered motility, each isolated in a distinct compartment enabling the use of the microgels as compartmentalized artificial cells. With this approach, the division of content and function seen in biological cells can be mirrored, which will underpin the generation of increasingly sophisticated and functional soft matter microdevices using bottom‐up synthetic biology principles.


Thermally Driven Dynamic Behaviours in Polymeric Vesicles as Biomimetic Synthetic Cell Systems

October 2024

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13 Reads

Synthetic cells have emerged as a promising tool for understanding cellular processes and developing novel biotechnological applications. In this study, we engineer dynamic and biomimetic behaviours in polymersomes, aiming to create synthetic cells that mimic key biological functions. These vesicles exhibit a temperature-driven fusogenic property, enabling the transformation of nanoscale vesicles into microsized sponge-like polymeric droplets. These droplets, rich in membrane content, can act as synthetic cells analogues with the capability for controlled cargo release. Moreover, the thermoresponsive nature of our polymersomes makes them versatile components for the construction of lipid-based synthetic cells, allowing for controllable cargo release and dynamic organelle-like functionalities. We also demonstrate that the microscale polymer droplets possess biomimetic properties including contractility, a behaviour typically observed in biological systems. By modulating the temperature, it is possible to induce these contractile behaviours as well as other functions, including controlled fusion and efficient bacteria capture.



Design of an intracellular aptamer-based fluorescent biosensor to track burden in E. coli

September 2024

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11 Reads

Cell burden impacts the performance of engineered synthetic systems. For this reason, there is great interest toward the development of tools to track burden and improve biotechnology applications. Fluorogenic RNA aptamers are excellent candidates for live monitoring of burden because their production is expected to impose a negligible load on transcription resources. Here we characterise the performance of a library of aptamers when expressed from different promoters in E. coli . We find that aptamer relative performance is dependent on the promoter and the strain, and that, contrary to expectation, aptamer expression impacts host fitness. By selecting two of the aptamers with brighter output and lower impact, we then design an intracellular biosensor able to report on the activation of the burden response in engineered cells. The sensor developed here adds to the collection of tools available for burden mitigation and may support bioprocessing applications where improved host performance is sought.


The ALS/FTD-related C9orf72 hexanucleotide repeat expansion forms RNA condensates through multimolecular G-quadruplexes

September 2024

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69 Reads

Amyotrophic lateral sclerosis (ALS) and frontotemporal dementia (FTD) are neurodegenerative diseases that exist on a clinico-pathogenetic spectrum, designated ALS/FTD. The most common genetic cause of ALS/FTD is expansion of the intronic hexanucleotide repeat (GGGGCC) n in C9orf72. Here, we investigate the formation of nucleic acid secondary structures in these expansion repeats, and their role in generating condensates characteristic of ALS/FTD. We observe significant aggregation of the hexanucleotide sequence (GGGGCC) n , which we associate to the formation of multimolecular G-quadruplexes (mG4s) by using a range of biophysical techniques. Exposing the condensates to G4-unfolding conditions leads to prompt disassembly, highlighting the key role of mG4-formation in the condensation process. We further validate the biological relevance of our findings by detecting an increased prevalence of G4-structures in C9orf72 mutant human motor neurons when compared to healthy motor neurons by staining with a G4-selective fluorescent probe, revealing signal in putative condensates. Our findings strongly suggest that RNA G-rich repetitive sequences can form protein-free condensates sustained by multimolecular G-quadruplexes, highlighting their potential relevance as therapeutic targets for C9orf72 mutation-related ALS/FTD. Amyotrophic lateral sclerosis (ALS) is rapidly progressive, uniformly fatal and untreatable due largely to an incomplete understanding of disease mechanisms. The lifetime risk of ALS is 1:300-1:400, and over an aggressive disease course, patients become paralysed, unable to eat, speak and breathe with an average survival of between 3-5 years 1. Frontotemporal dementia (FTD) is the second most common cause of dementia in patients less than 65 years old and is increasingly recog-nised to share clinical, genetic and pathomechanistic features with ALS, termed ALS/FTD 2. ALS and FTD, much like other neurodegen-erative diseases, are characterised by the presence of pathological aggregates in neurons. Many existing studies have predominantly focused on the protein component as the leading aggregation trigger 3 ,


Nucleated synthetic cells with genetically driven intercompartment communication

August 2024

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17 Reads

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1 Citation

Proceedings of the National Academy of Sciences

Eukaryotic cells are characterized by multiple chemically distinct compartments, one of the most notable being the nucleus. Within these compartments, there is a continuous exchange of information, chemicals, and signaling molecules, essential for coordinating and regulating cellular activities. One of the main goals of bottom–up synthetic biology is to enhance the complexity of synthetic cells by establishing functional compartmentalization. There is a need to mimic autonomous signaling between compartments, which in living cells, is often regulated at the genetic level within the nucleus. This advancement is key to unlocking the potential of synthetic cells as cell models and as microdevices in biotechnology. However, a technological bottleneck exists preventing the creation of synthetic cells with a defined nucleus-like compartment capable of genetically programmed intercompartment signaling events. Here, we present an approach for creating synthetic cells with distinct nucleus-like compartments that can encapsulate different biochemical mixtures in discrete compartments. Our system enables in situ protein expression of membrane proteins, enabling autonomous chemical communication between nuclear and cytoplasmic compartments, leading to downstream activation of enzymatic pathways within the cell.


Rapid manufacturing and assembly of our CO2 laser cut device. a) Laser cutting. Parts designed in CAD were laser cut from 5 mm thick sheets of i) plain PMMA or ii) PMMA prepared with double-sided adhesive. b) Assembly. i) The phase transfer column was assembled via the double-sided adhesive and ii) relevant holes (indicated by the arrows) were threaded using an M2 hand tap. iii) A glass slide was fixed to the base of the phase transfer column using double sided adhesive and nylon screws (with their heads removed) were inserted into the threaded holes to support the installation of a tray for moving the electrodes in the forward and backward directions. iv) Nylon screws (with their heads removed) were inserted into the threaded holes of the tray to support a second tray (with a cavity for the electrode holder) for moving the electrode up and down. A top bracket was installed to secure the assembly and to support an M2 screw that was threaded through the second tray. After the addition of nylon nuts in the indicated positions, the platform could be raised or lowered by turning the indicated screw clockwise our counterclockwise. v) Electrode holders housing Ag/AgCl electrodes were inserted into the cavities by push fit. c) A photograph of our setup placed inside our Faraday cage
Device operation (illustrations show cross-sectional view). a) The Ag/AgCl electrode connected to the input of the amplifier was lowered into the upper section of the phase transfer column containing lipid–oil. The insert shows a magnified illustration of the phase transfer column (not to scale). i) Capacitance measurements in this configuration show a background capacitance of ∼8 pA while bilayer current measurements at +100 mV in ii) show a baseline around 0 pA. b) Illustration showing the measuring electrode after being lowered down the phase transfer column and through the oil : water interface after a 10-minute incubation, alongside an insert showing a magnified perspective (not to scale). i) Capacitance measurements in this configuration either show saturation (indicating the absence of a lipid bilayer), or a bilayer capacitance (as shown). ii) Bilayer current measurements at +100 mV either showed saturation in this configuration, or bilayer currents of several nA. Bilayer current traces were captured using the 20 nA range on the amplifier, a sampling rate of 20 kHz and a final bandwidth of SR/20. They were also digitally filtered using a low-pass Gaussian filter with a cut-off frequency of 1 kHz
Bilayer functionalisation with nanopores and blockers. a) Representative trace showing the bilayer current becoming more permeable to ion flow in the presence of αHL. b) Trace showing the reversal of additional bilayer current when in the presence of TRIMEB (green circles). Bilayer current traces were captured using the 20 nA range on the amplifier, a sampling rate of 20 kHz and a final bandwidth of SR/20. They were also digitally filtered using a low-pass Gaussian filter with a cut-off frequency of 1 kHz
Control of bilayer area by lowering the measuring electrode to different positions though the oil–water interface. Data points correspond to translation distances of 1.5 mm (n = 3, squares), 2.0 mm (n = 6, circles), 2.5 mm (n = 5, triangles) and 3.0 mm (n = 4, diamonds). The data shows that the area of the bilayer increases with translation distance. Illustrations do not show the ground electrode
A handheld laser-cut device for the size-controlled assembly and electrical characterisation of lipid bilayers

July 2024

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10 Reads

We report the rapid fabrication of a handheld laser cut platform that can support the assembly, functionalisation, size-control and electrical characterisation of lipid bilayers. We achieve this by building a modular DIY platform that can support the lowering of a Ag/AgCl electrode through a phase transfer column consisting of an upper oil phase containing lipids, and a lower aqueous phase containing buffer.


Engineering a nanoscale liposome-in-liposome for in situ biochemical synthesis and multi-stage release

July 2024

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140 Reads

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10 Citations

Nature Chemistry

Soft-matter nanoscale assemblies such as liposomes and lipid nanoparticles have the potential to deliver and release multiple cargos in an externally stimulated and site-specific manner. Such assemblies are currently structurally simplistic, comprising spherical capsules or lipid clusters. Given that form and function are intertwined, this lack of architectural complexity restricts the development of more sophisticated properties. To address this, we have devised an engineering strategy combining microfluidics and conjugation chemistry to synthesize nanosized liposomes with two discrete compartments, one within another, which we term concentrisomes. We can control the composition of each bilayer and tune both particle size and the dimensions between inner and outer membranes. We can specify the identity of encapsulated cargo within each compartment, and the biophysical features of inner and outer bilayers, allowing us to imbue each bilayer with different stimuli-responsive properties. We use these particles for multi-stage release of two payloads at defined time points, and as attolitre reactors for triggered in situ biochemical synthesis.


Citations (49)


... [94] In a similar vein, DNA nanopores were incorporated onto a vesicle membrane to serve as a transmembrane protein analog, [96] which enabled complementary pairing between the receptor vesicle nanopore and a single-stranded DNA messenger, opening the nanopore to facilitate ion transfer across the membrane. Another interesting approach to non-contact signaling involves multi-compartment vesicles, [97][98][99][100][101][102][103] where multiple compartments are encapsulated within a single droplet. As the spatial crowding within these compartments increases, signal transmission becomes faster and more efficient. ...

Reference:

Engineering Protocell Networks for Prototissue Development
Engineering a nanoscale liposome-in-liposome for in situ biochemical synthesis and multi-stage release

Nature Chemistry

... This hierarchical development highlights how progress in bottom-up technologies can provide ways to reliably encapsulate small molecules [39] and assemble complex macromolecular structures such as the cytoskeleton and cell division machinery [40]. These incremental developments in the complexity of SCs have far-reaching applications beyond biomedical research, for example as biosensors [41] or to deliver active agents [6,42] for practical applications. However, the droplet transfer method is not without its drawbacks (Box 1). ...

Genetically programmed synthetic cells for thermo-responsive protein synthesis and cargo release

Nature Chemical Biology

... This localised heating, termed magnetic hyperthermia, is clinically-approved to ablate malignant tumours by exploiting the differing heat tolerance between tumour and healthy 30 cells, whereby healthy cells can survive above physiological temperature for longer (15). Magnetic hyperthermia has also been investigated for rupturing lipid bilayers, but it demands high frequencies that are neither clinically tolerable nor compatible with current medical AMF generators (16)(17)(18)(19). Additionally, the disruption of bilayers limits their potential use with synthetic cells and CFPS. ...

Magnetic Modulation of Biochemical Synthesis in Synthetic Cells
  • Citing Article
  • May 2024

Journal of the American Chemical Society

... 15 One of the applications of DNA origami is the creation of dynamic structures, achieved through various methods. [16][17][18][19] These structures are utilized in diverse fields, such as biosensing, 20,21 bioimaging, 22 the design of DNA origami-based vaccines 23 or their use in nanovaccines, 24 smart drug delivery systems, [25][26][27] biomolecular computing, 28 and the development of nanodevices that can be externally manipulated using light or other electromagnetic fields. [29][30][31] The wireframe DNA origami method, one of the design techniques in DNA origami technology, was first introduced by Zhang in 2015. ...

Lipid vesicle-based molecular robots

Lab on a Chip

... The engineering approach is used to obtain desired functions or specifications and serves two main goals: to gain a detailed understanding of biological mechanisms, and to produce useful bio-based applications and materials [5]. Designing autonomous self-reproducing SCs should first of all address important questions concerning how life works, but also allow for practical applications [6]. In a top-down approach to SCs, a living bacterium's genome is replaced with a minimized synthetic one, reprogramming the cell and making space for designed elements and functions [7][8][9]. ...

Present and future of synthetic cell development
  • Citing Article
  • December 2023

Nature Reviews Molecular Cell Biology

... Filtering for unspecific gene expression inhibitors turned out to be essential, since ca 50% of the primary hits were interfering with the canonical gene expression machineries. Our high hit rate of transcription inhibitors is consistent with a very recent report of a small screen with a focused library of 1430 approved drugs for RAN DPR modulation in iPSC neurons which identified nucleoside analogs resulting in both, reduction of RAN DPRs as well as G4C2 RNA [ 100 ]. Furthermore, we observed that G4C2-repeat containing foci are dynamic structures with a high turnover and T 1 / 2 of ca. 4 h that are pharmacologically tractable. ...

The ALS/FTD-related C9orf72 hexanucleotide repeat expansion forms RNA condensates through multimolecular G-quadruplexes

... Besides tuning the lipid components in LNP formulations to achieve extrahepatic delivery, altering the surface properties of LNPs by directly adding targeting ligands or moieties also shows potential in directing LNPs to extrahepatic organs. Additionally, as usual, the surface-decorated moieties have an innate affinity for specific cellular receptors or membrane proteins; the surface-modified LNPs facilitate the accumulation of LNPs not only in certain organs but also in specific cells [86,87]. ...

Modular Bioorthogonal Lipid Nanoparticle Modification Platforms for Cardiac Homing

Journal of the American Chemical Society

... The concept of organelles is also starting to be applied to artificial cells [18][19][20] . These artificial organelles in the artificial cell will offer chemically isolated space for specific reactions, thereby enabling spatial arrangement of modular functions and higher-order organization of complex chemical systems closer to the framework of living organisms. ...

Biomimetic behaviors in hydrogel artificial cells through embedded organelles
  • Citing Article
  • August 2023

Proceedings of the National Academy of Sciences

... In the future, such technologies could shatter the "aura" of life as we know it [14] and make us rethink some fundamental categories and practices [20]. Scientists working on bottom-up SCs currently consider them not alive, "not quite alive", or as a "proxy for life" [6, p. 162, 166; 79], the main criteria of "aliveness" being autonomous self-replication and life-like behavior [79]. A range of approaches to assessing the "life-likeness" of SCs (such as Turing test) is currently under discussion [80,81]. ...

What it means to be alive: a synthetic cell perspective

... Consequently, the increasing polarity of their surrounding environments triggers the rearrangement of the micellar disk intermediates into lipid vesicles by the hydrophobic effect. 73 . Lyotropic liquid crystalline (LLC) nanoparticles (cubosomes and hexosomes) were produced rapidly and continuously with tunable sizes controlled by flow rate ratio (FRR). ...

A microfluidic platform for the controlled synthesis of architecturally complex liquid crystalline nanoparticles