Alex Ross’s research while affiliated with University of Ottawa and other places

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Publications (12)


Multipurpose On‐the‐Spot Peptide‐Based Hydrogels for Skin, Cornea, and Heart Repair (Adv. Funct. Mater. 37/2024)
  • Article

September 2024

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19 Reads

Alex Ross

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Xixi Guo

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[...]

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Emilio I. Alarcon

Engineered peptides for on‐the‐spot soft tissue repair. A) Left: Schematic depiction for the strategy used in this study for the in situ assembling of the materials. Assembly of the hydrogel takes place within minutes at room temperature. Some of the key chemical motifs of the material components are depicted at the bottom of the schematic. Right: Flow diagram showing the tests used to screen material formulations. This methodology was designed to narrow down the number of candidate formulations. B–H) Heatmaps are used to display changes in the properties measured following the schematic in Figure 1A. Each figure contains a colour scale illustrating changes in the parameters of materials with different CMratio and peptide formulations (abbreviated as Pep, raw data available in Table S2 (Supporting Information), n = 5) for: (B) Left: gelation time (s) and Right: Representative still images of two selected peptide formulations (50 µL, CMratio of 4.0) taken at 0, 30, and 45s after positioning the samples at a 45° inclination. Scale bar is 2 mm; (C) Transmittance (%); (D) refractive index; (E) denaturation temperature (°C); (F) water content (%); (G) collagenase degradation (mg h⁻¹); and. (H) Left: ATR‐FTIR (with the respective deconvoluted Gaussian fit) spectra of selected peptides at CMratio 1.0, where the light blue peaks correspond to the different Amide I signal of each peptide, and the light red and violet peaks correspond to the C = O and C = C of PEG‐MAL, respectively. Experimental details are in the Materials and Methods and the Supplementary Information.
Peptide‐based materials can be used to bond tissues better than current commercially available products. A) Left: 3D renders for the custom‐designed hand‐held device for delivering the peptide‐based materials designed in this study. The render displays the main features of the device that include: (1) dispensing on/off control, (2) enclosed compartment for placing peptide‐cartridges (preloaded syringes), (3) aperture for nozzle adapters, (4) camera port for live monitoring, and (5) digital controller screen for volume and speed settings. Right: Three representative nozzles designed for the hand‐held device presented herein for topical application (left), cornea sealant delivery (middle), and intratissue injection (right). B) Schematic depiction for the procedure followed to assess skin bonding in a full‐thickness incision. Bonded tissue was assessed using uniaxial mechanical stretching tests perpendicular to the wound. Bonding strength was measured an hour after application for Figures 2C, D, and F. C) Mechanical strength (kPa), also known as wound closure strength test (ASTM F2458), measured for murine skin tissue after application of peptide‐based formulations CMratio 4.0 (10 mm min⁻¹ extension) for top peptide‐based hydrogels prepared using peptide 3, 4, and 5. Values measured for applications of BioGlue® and the collagen‐like peptides (CLP) are also included in the plot (n = 7‐8). D) Mechanical strength (kPa) for murine skin tissue measured using the 4.0 ratio at two different dilutions (½ and ¼; n = 3‐5). E) Changes in bond strength as a function of time post‐application (10, 30, and 60 min). Samples were incubated at 37°C in 100% humidity (n = 3‐4). F) Left: Illustration for lap‐shear tests using porcine skin using a 10 mm min⁻¹ extension. The adhesion surface was fixed at 50 mm². The adhesive (peptide‐based formulation or BioGlue®) was applied within the two pieces of skin. Right: Adhesion strength values measured for the peptide‐based formulation CMratio 4.0 and BioGlue® (n = 3‐4, ≈50 µm thickness for the peptide or BioGlue®). P‐values for C, D, and F were calculated using One‐Way ANOVA and a post‐hoc Holmes correction. P‐values for F were calculated using a student t‐test (unpaired unequal variance).
Peptide‐based materials as tissue bonding sealants and fillers. A) Schematic of the experimental design used for the in vivo testing of the tissue bonding capabilities of the peptide‐based materials using C57BL/6 female mice (7‐8 weeks). B) Representative images of the full‐thickness wounds taken at 0‐, 1‐, 3‐, and 7‐days post‐treatment for the different experimental groups. Scale bars = 5.0 mm. C) Mechanical strength (kPa) for murine skin tissue measured 7 days post‐operation (n = 5–8) obtained for the different experimental groups. The Sham group corresponds to animals that underwent the same steps as those that received incisions, but the skin remained intact. D) Left: representative histological images of the skin at 7 days for the 3 treatment groups. Right: Analysis of the histological sections obtained for the different treatment groups including collagen deposition (n = 4–16), and epidermal thickness (n = 11–16).[55–57] E) Left: Burst pressure values measured for the peptide‐based material CMratio 4.0 or cyanoacrylate (n = 5–17). Right: Illustration for the pig cornea perforation ex vivo model used in this study. The numbers in the Figure illustrate: (1) initial perforation to create a wound bed, (2) inner full‐thickness cornea perforation using a 1 mm biopsy puncher, (3) application of the treatment to seal the hole, and (4) formation of a “corneal” patch. F) Changes in implant thickness were obtained using 30 µL of the CMratio 4.0 peptide material or Viscoat (n = 5). G) Left: Illustration of the ex vivo pig cornea pocket and cornea reshaping model used in this study. The numbers in the figure illustrate: (1) initial surgical incision to create a wound bed, (2) insertion of needle to open a cavity, (3) injection of the peptide‐based material as an intracorneal patch, and (4) positioning of a solid contact lens. Right top: Representative corneal topographic axial maps showing surface elevation of corneas injected with either CMratio 4.0 or Viscoat. The topographic maps are generated for corneas before injection, after injection, and injection in conjunction with insertion of a rigid contact lens (Centracone). The scale on the right shows the height in mm, with warmer colors representing steeper areas and cooler colors marking flatter ones. Right bottom: Fold change for K values of curvature (mm) obtained for corneas that have been injected with either CMratio 4.0 or Viscoat, with the placement of RGP/Centracone rigid contact lenses in conjunction with the peptide‐based material (n = 4) with volumes ≈30 µL (compared to empty pocket). For C and D, p values were calculated using One‐Way ANOVA and post‐hoc Holmes test, while student t‐tests were used for E and F (unpaired unequal variance) and G (paired data).
Peptide‐based materials can be safely injected intramyocardially and remain within the cardiac muscle. A) Schematic of the experimental design for in vivo testing of the intramyocardial injection application of the peptide‐based materials. Experiments were carried out using C57BL/6 female mice (7‐8 weeks). B) Percentage of live human cardiac endothelial cells measured at 0 and 2 days after seeding on the CMratio 1.0 material or collagen‐based hydrogel (n = 5‐9). C) Left ventricular ejection fraction (LVEF) fold change relative to baseline measured 28 days after treatment with CMratio 1.0 material or PBS (n = 4‐5). D) Left: Representative Masson trichrome staining images for hearts treated with CMratio 1.0 material or PBS. Right: Analysis of the scar size for the two treatment groups (n = 5). E) Number of CD206⁺ cells counted in myocardial tissue sections within the scar, border zone, and remote areas (n = 6). F) Left: Quantification for ex vivo fluorescence imaging (λexcitation = 570 nm; λemission = 640 nm) of hearts injected with the Alexa‐Fluor@594‐labelled CMratio 1.0 material at different days post‐injection. Right: Representative IVIS images of the MI hearts harvested after 2‐ or 7‐days post‐injection (n = 3). P values were calculated using student t‐test (unpaired data & unequal variance).
Multipurpose On‐the‐Spot Peptide‐Based Hydrogels for Skin, Cornea, and Heart Repair
  • Article
  • Full-text available

April 2024

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205 Reads

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1 Citation

Bioinspired synthetic materials can be designed as reliable, cost‐effective, and fully controlled alternatives to natural biomaterials for treating damaged tissues and organs. However, several hurdles need to be overcome for clinical translation, particularly for biomaterials gelled in situ. These include the potential toxicity of chemical crosslinkers used in the materials' assembly or breakdown products they generate and the challenges of fine‐tuning the mechanical properties of the materials. Here, a minimalistic, adhesive soft material is developed by screening hundreds of potential formulations of self‐assembling, custom‐designed collagen‐like peptide sequences for the in situ formation of tissue‐bonding 3D hydrogels. Nine promising formulations for tissue repair are identified using a low‐volume and rapid combinatory screening approach. It is shown that simply varying the ratio of the two key components promotes adhesion and fine‐tunes the material's mechanical properties. The materials' skin and heart repair capabilities are assessed in vitro and clinically relevant animal models. The materials are also tested for corneal applications using ex vivo pig cornea models complemented by in vitro cell compatibility assays.

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Schematic research strategy followed in this work. Top: Steps 1 and 2: Development of a low dosage blue‐light activated material for in situ corneal repair using collagen‐like peptides (CLPs) to replace gelatin, the initial test polymer. Step 3 depicts the creation of a library for the different compositions of the formulations. Pulses of blue light were applied in steps 2, 6 and 7. Bottom: Custom‐designed peptides with photoreactive moieties used in this study.
Using GelMa to identify the optimal composition for a peptide‐based light‐activated cornea filler. A) Schematic depiction for the main steps used in the preparation of the light activated materials. Left: Pre‐cross‐linking step to increase viscosity produce materials that can withstand the high intracorneal pressure immediately post‐injection and can be rapidly crosslinked using blue light. Middle: Precrosslinked formulation dispensed in a 96‐well plate to be irradiated under low oxygen concentration and high humidity. Right: Irradiation of the samples with a fiber optic blue light source (total energy dose of 2.5 J cm⁻²). B) Total light dosage needed to pre‐crosslink (PXL) the formulations composed of 8‐Arms‐PEG acrylate, chondroitin methacrylate, hyaluronic acid methacrylate, and gelatin methacrylate, concentrations expressed in % w/v. C) Total light dosage needed to pre‐crosslink (PXL) the formulations composed of 8‐Arms‐PEG acrylate, chondroitin methacrylate, hyaluronic methacrylate, and gelatin methacrylate with and without APS/TEMED. D) Total light dosage needed to solidify the formulations composed of 8‐Arms‐PEG acrylate, chondroitin methacrylate (CSMA), hyaluronic acid methacrylate (HAMA), and our custom‐designed peptides (see main text for further details). E) Light transmittance (380 nm‐750 nm) for the formulations prepared using our custom‐made peptide formulations. F) Water content of the top four hydrogel candidates swollen in dextran solution for 1 day or 2 weeks and synthesized from either freshly prepared injectable formulations or formulations stored at 4 °C for 5 weeks shielded from light.
Peptide‐based materials have suitable physical and biocompatible properties as intrastromal corneal bulking agents. A) Top: Viscosity as a function of shear rate (s⁻¹) measured for the four different peptide‐based formulations and for Viscoat®. Bottom: Compression moduli for fully crosslinked materials (n≥3). Data showed the plot are represented as box plots where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set that fall within an acceptable range. B) Top: Schematic depiction for the main steps used in the ex vivo testing of the injectable materials (all samples were in situ crosslink 2.5 J cm⁻²). Bottom left: Average thickness of the injected formulations measured from OCT images at different time points post‐injection (n = 3). Bottom right: Average thickness of the injected G44 formulations using different volumes (10, 30, and 50 µL). Thickness was measured using OCT 48 h post injection (n≥ 3). C) Pachymetry map pre and postop. Maps 1 and 2 underline the fact that porcine corneas are thicker than human corneas (pink color above the standard threshold for human corneas). Map 3 shows difference map showing the increase in pachymetry generated by the photocrosslinked implant. The blue marks show that the central pachymetry increased by 190 µm (from 1013 to 1203 µm). Distribution of the thickening however is not uniform. Plot 4 shows Axial/Sagittal curvature difference map that displays an asymmetry of the front corneal surface curvature, which is flatter (−16.3 Diopters) over the inferior thicker zone of the implant and steeper (+22.5 Diopters) on the opposite side of the cornea. D) Number of live human‐ corneal epithelial cells per field of view (FOV) measured after 48 h seeding on pre‐made peptide‐based formulations hydrogels (n≥ 3). Representative images for Live/Dead assay can be found in Supporting Information Figure S16 (Supporting Information).
Performance of peptide‐based materials as corneal bulking agent in rats. A) Schematic illustrating the protocol used to thicken rat corneas in vivo. B) Peptide‐based materials did not promote corneal vascularization and all corneas healed with minimal scarring. Cornea transparency was monitored after biomaterial intrastromal injection over 6‐week period. C) Peptide‐based materials remained stable overtime after intracorneal injection in a rat model. OCT images of rat corneas (G44‐A and B; G50‐D, and F) at different time points before and after surgery illustrate retention of the injected hydrogels within the corneal stroma 6 weeks post operation. In two corneas (G44‐C and G50‐E) the injected hydrogel was lost shortly after surgery. Higher resolution in vivo OCT images (Figure S22, Supporting Information) were obtained at the end of the study. They confirmed with greater detail the anatomy of the injected corneal tissue and implants. Scale bars: 1.0 mm. D) Histology 6 weeks after intracorneal injection in a rat model assessed 6 weeks post injection. Hematoxylin and eosin staining shows the retention of the changed shape of the cornea in two rats after injection with the bulking agents (G44‐A and G50‐D). In the same two corneas, picrosirius red and alcian blue confirmed the presence of the glycosaminoglycans component of the hydrogels. The bright Picrosirius red fluorescence clearly shows the red of the rat corneal stromal layers around the bulking agent. The arrows in the G50‐D treated corneas show incorporation of hydrogel into the spread corneal lamellae. The unoperated corneas had normal histology as shown by the hematoxylin and eosin, picrosirius red and alcian blue. All images were processed in FIJI. Scale bars: 50 µm.
Low Energy Blue Pulsed Light‐Activated Injectable Materials for Restoring Thinning Corneas

July 2023

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229 Reads

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7 Citations

Many alternatives to human donor corneas are being developed to meet the global shortage of donated tissues. However, corneal transplantation remains the gold standard for diseases resulting in thinning corneas. In this study, transparent low energy photoactivated extracellular matrix‐mimicking materials are developed for intrastromal injection to restore stromal thickness. The injectable biomaterials are comprised of short peptides and glycosaminoglycans (chondroitin, hyaluronic acid) that assemble into a hydrogel when pulsed with low‐energy blue light. The dosage of pulsed‐blue light needed for material activation is minimal at 8.5 mW cm⁻², thus circumventing any blue light cytotoxicity. Intrastromal injection of these light‐activated biomaterials in rat corneas shows that two iterations of the formulations remain stable in situ without stimulating significant inflammation or neovascularization. The use of low light intensities and the ability of the developed materials to stably rebuild and change the curvature of the cornea tissue make these formulations attractive for clinical translation.



Schematic representation of selected biological and non-biological materials used for tissue regeneration: (A) alginate; (B) chitosan; (C) silk; (D) hyaluronic acid; (E) type II-collagen; (F) elastin; (G) fibrin; (H) graphene oxide; (I) poly(Lactide-co-Glycolide) (J) poly(ethylene glycol).
Schematic representation for the interactions between materials and peptides. Peptides can be added to a biomaterial through 1) simple adsorption, 2) covalent conjugation, 3) molecular interactions, 4) entrapment, or through 5) chemical modifications.
Peptide Biomaterials for Tissue Regeneration

August 2022

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114 Reads

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7 Citations

Expanding the toolbox of therapeutic materials for soft tissue and organ repair has become a critical component of tissue engineering. While animal- and plant-derived proteins are the foundation for developing biomimetic tissue constructs, using peptides as either constituents or frameworks for the materials has gained increasing momentum in recent years. This mini review discusses recent advances in peptide-based biomaterials’ design and application. We also discuss some of the future challenges posed and opportunities opened by peptide-based structures in the field of tissue engineering and regenerative medicine.


The histone H3.1 variant regulates TONSOKU-mediated DNA repair during replication

March 2022

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169 Reads

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39 Citations

Science

The tail of replication-dependent histone H3.1 varies from that of replication-independent H3.3 at the amino acid located at position 31 in plants and animals, but no function has been assigned to this residue to demonstrate a unique and conserved role for H3.1 during replication. We found that TONSOKU (TSK/TONSL), which rescues broken replication forks, specifically interacts with H3.1 via recognition of alanine 31 by its tetratricopeptide repeat domain. Our results indicate that genomic instability in the absence of ATXR5/ATXR6-catalyzed histone H3 lysine 27 monomethylation in plants depends on H3.1, TSK, and DNA polymerase theta (Pol θ). This work reveals an H3.1-specific function during replication and a common strategy used in multicellular eukaryotes for regulating post-replicative chromatin maturation and TSK, which relies on histone monomethyltransferases and reading of the H3.1 variant.


Figure 2. (a) Schematic representation of the main steps involved in the preparation of the nanoengineered spray-on therapeutic. Note that sprayed volumes were 4.0 μL in all cases. (b) Uniformity of spray-on pattern at three different distances from the target surface. Left top: Representative photographs of spray patterns obtained at distances of 4, 2, and 1 cm. Scale bar = 1 cm. Left middle: 3D surface plot illustrating the intensity of spray patterns as measured using Image-J. Left bottom: Intensity profile of a transverse section of the spray pattern. Right: Full width halfmaximum (fwhm) of the spray patterns as measured from the profile plots. n = 4, for all groups, ** p ≤ 0.01 and *** p ≤ 0.001 calculated via ANOVA with Tukey posthoc analysis. (c) Surface plasmon absorption of a type I collagen hydrogel pre-and postmodification with the Multi peptide modified nanogold sprayon. Insets: Representatives images for the type I collagen surfaces with and without the spray-on treatment. The red arrows in the top image outline the region that received the spray-on treatment. (d) Electrical resistivity for collagen matrices treated and embedded with peptide-modified nanogold. P values were calculated using a t test (n = 3). Values in (c) are represented as box plots where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set.
Figure 3. (a) Schematic of the in vivo study timeline. The different treatments were sprayed onto the surface of the infarcted myocardium at 7 days post-MI. (b) LVEF at 28 days post-treatment. Note that the horizontal blue line represents values for SHAM mice. (c) Fold change in LVEF at 28 days post-treatment. (d) ESV fold change at 28 days post-treatment. (e) EDV fold change at 28 days post-treatment. (f) Endocardial longitudinal strain reached at aortic valve closure within the anterior apex segment at 28 days post-treatment. Note that the horizontal blue line represents values for SHAM mice. (g) Sample ECG profiles for the different treatment groups collected at 28 days posttreatment. (h) QRS interval in ms, calculated from ECG signals at 28 days post-treatment. Note that the horizontal blue line represents values for SHAM mice. (i) Total gold content determined in selected organs collected 28 days post-treatment (n = 3). Values in (b−f, h, and i) are represented as box plots where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set. Otherwise indicated group sizes were, n = 6−12. P values for (b−h) were calculated via ANOVA with Holms posthoc analysis. P values for (i) were calculated via t test for unpaired data with unequal variance. The scheme in (a) was generated using Biorender.
Figure 4. (a) Representative images of Masson's trichrome stained cardiac tissue sections treated with PBS, AuNP, 4-Leg, Multi, 4-Leg AuNP and Multi AuNP. Scale bar = 2 mm. (b) Remote wall thickness of the myocardium measured in Masson's trichrome stained tissue sections at 28 days post-treatment. (c) Scar size (% LV) measured at 28 days post-treatment in Masson's trichrome stained tissue sections. Values in (b and c) are represented as box plots, where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set. P values were calculated via ANOVA with Holms posthoc analysis. Group sizes n = 6−12.
Figure 5. (a) Representative immunohistochemistry images and quantification of double positive α-SMA + (green) and CD31 + (red) arterioles, CD31 + capillaries (red), and DAPI-stained cell nuclei (blue). Scale bar = 100 μm. Representative images for the treatment groups not shown in the main manuscript can be found in Figure S11. (b) Representative immunohistochemistry images and quantification of CD86 + proinflammatory macrophages (green) and CD206 + prowound healing macrophages (green). Scale bar = 100 μm. Representative images for the treatment groups not shown in the main manuscript can be found in Figure S12. Values plotted are presented as the number of cells/mm 2 represented in box plots, where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box indicate the minimum and maximum values within the data set that fall within an acceptable range. P values were calculated via ANOVA with Holms posthoc analysis. Samples sizes n = 6 for each treatment group.
Figure 6. (a) Representative immunohistochemistry staining images for cTnT and Cx43 in the border zone after treatment with PBS, AuNP, 4-Leg, Multi, 4-Leg AuNP, and Multi-AuNP; red: cTnT, green: Cx43, blue: DAPI. Scale bar = 100 μm. (b) Quantification of total cTnT positive area (in mm 2 ). (c) Quantification of Cx43 cells in the remote area. Values in (c) are represented as box plots, where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set. Statistical values were determined by one-way ANOVA using Holm's posthoc analysis. Samples sizes n = 6 for each group.
Nanoengineered Sprayable Therapy for Treating Myocardial Infarction

February 2022

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238 Reads

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9 Citations

ACS Nano

We report the development, as well as the in vitro and in vivo testing, of a sprayable nanotherapeutic that uses surface engineered custom-designed multiarmed peptide grafted nanogold for on-the-spot coating of an infarcted myocardial surface. When applied to mouse hearts, 1 week after infarction, the spray-on treatment resulted in an increase in cardiac function (2.4-fold), muscle contractility, and myocardial electrical conductivity. The applied nanogold remained at the treatment site 28 days postapplication with no off-target organ infiltration. Further, the infarct size in the mice that received treatment was found to be <10% of the total left ventricle area, while the number of blood vessels, prohealing macrophages, and cardiomyocytes increased to levels comparable to that of a healthy animal. Our cumulative data suggest that the therapeutic action of our spray-on nanotherapeutic is highly effective, and in practice, its application is simpler than other regenerative approaches for treating an infarcted heart.


Mimicking biofilm formation and development: Recent progress in In Vitro and In Vivo biofilm models

April 2021

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1,969 Reads

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191 Citations

iScience

Biofilm formation in living organisms is associated to tissue and implant infections and it has also been linked to the contribution of antibiotic resistance. Thus, understanding biofilm development and being able to mimic such processes is vital for the successful development of anti-biofilm treatments and therapies. Several decades of research have contributed to building the foundation for developing in vitro and in vivo biofilm models. However, no such thing as an “all fit” in vitro or in vivo biofilm models is currently available. In this review, in addition to presenting an updated overview of biofilm formation, we critically revise recent approaches for the improvement of in vitro and in vivo biofilm models.


Design of nanoparticle flow synthesis system. Left: Schematic representation for the Nanoparticle Flow Synthesis System (NPFloSS). Right: Actual pictures of the NPFloSS highlighting some key components of the design. The NPFloSS is composed of three simple main components: (1) a UV-transparent quartz cell with connected by tubing, (2) two 365 nm UVA LEDs as a photon source, and (3) two heat sinks for heat management. The part list information and assembly instructions for this system are available at no cost in the ESI of the article.
Colloidal properties for nanogold and nanosilver solutions prepared using NPFloSS. NPFloSS allows for rapid nanogold and nanosilver synthesis. Absorption spectra for nanogold (A) and nanosilver (B) aqueous colloidal solutions prepared using NPFloSS; gold nanoparticles capped with bovine serum albumin and silver nanoparticles capped with CLKRS peptide. The spectra illustrate representative examples for the determination of tau, the wavelength of maximal plasmon band absorbance, and full width at half maximum (FWHM) of the plasmon band. (C,D) from top to bottom: Hydrodynamic size, zeta potential, Tau, and FWHM values for gold (C) and silver (D) nanoparticles prepared in the presence of different protecting agents (see Scheme 1 for synthesis protocol). For each different equivalency of protecting agent, three batches were produced and measured in triplicate. Values in plots (C,D) are represented as box plots where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set that fall within an acceptable range. Sample size is n = 3 in all cases. See Table S3 for statistical analysis.
Transmission electron microscopy images for nanogold and nanosilver prepared using NPFloSS. Nanogold TEM measurements corroborate DLS measurements with regards to particle size for nanoparticle samples made by NPFloSS. The type of nanoparticle, capping agent used, and number of equivalents for the capping agent are presented to the left side of each histogram. Each histogram represents 30–100 individually measured nanoparticles. Representative TEM images of the nanoparticles are shown to the right of each histogram along with a 100 nm scale bar. Values in the figure are represented as box plots where the box encloses 50% of the data, upper and lower quartile, with the median value of the variable displayed as a line inside the box. The bars extending from the top and bottom of each box mark the minimum and maximum values within the data set that fall within an acceptable range. p values are calculated by one-way ANOVA using Holm's multiple comparison analysis. Bars in red indicate no statistically significant differences (see Table S5).
Optimized schematic representation for operation of the Nanoparticle Flow Synthesis System (NPFloSS). For nanogold (top) or nanosilver (bottom).
A low cost and open access system for rapid synthesis of large volumes of gold and silver nanoparticles

March 2021

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95 Reads

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20 Citations

Rapid synthesis of nanomaterials in scalable quantities is critical for accelerating the discovery and commercial translation of nanoscale-based technologies. The synthesis of metal nanogold and silver in volumes larger than 100 mL is not automatized and might require of the use of harsh conditions that in most cases is detrimental for the production of nanoparticles with reproducible size distributions. In this work, we present the development and optimization of an open-access low-cost NanoParticle Flow Synthesis System (NPFloSS) that allows for the rapid preparation of volumes of up to 1 L of gold and silver nanoparticle aqueous solutions.


Citations (8)


... They shield new cells from external harm, promote cell growth and movement, and reduce scar formation. [10][11][12] Gelatin (Gel) stands out among hydrogel materials for skin repair due to its biocompatibility and biodegradability. For instance, Lu 13 employed a Schiff base reaction to combine a complex formed by iron ions and 2,3,4-trihydroxybenzaldehyde with a gelatin hydrogel, thereby creating a composite hydrogel with antibacterial and anti-inflammatory properties. ...

Reference:

Curcumin-Loaded Nanocomposite Hydrogel Dressings for Promoting Infected Wound Healing and Tissue Regeneration
Multipurpose On‐the‐Spot Peptide‐Based Hydrogels for Skin, Cornea, and Heart Repair

... As an ex vivo model, we chose a cornea perforation system, which is readily used to test the suitability of a material for sealing a perforated tissue. [52] Figure 3E depicts the data and schematic representation for the ex vivo model we used. Pig corneas were used as they are physiologically similar to humans. ...

Low Energy Blue Pulsed Light‐Activated Injectable Materials for Restoring Thinning Corneas

... In this study, we attempted to develop β-catenin-derived peptides containing one or more mutations through structural analysis of the β-and α-catenin complex with the ability to bind α-catenin. Peptides are a type of biomaterial consisting of 2-50 amino acids that forms a polymer chain with different structures such as α-helix or β-sheet [28,29]. Due to their higher efficacy and specificity and lower adverse effect and toxicity, peptides are emerging as a promising therapeutic option in drug discovery and development [30][31][32][33][34][35][36][37]. ...

Peptide Biomaterials for Tissue Regeneration

... During DNA replication, the repair of broken replication forks is also tightly controlled by histone modifications (Fig. 5b). In atxr5/6 mutants, deficiency in H3K27me1 deposition leads to re-replication of heterochromatin 115 through the activation of the DDR 116 : TONSOKU (TSK), a key player in the initiation of HR-mediated repair at stalled replication forks, binds exclusively to unmethylated histone H3.1 and facilitates the recruitment of Polθ, the DNA polymerase responsible for alt-NHEJ 117 . Newly incorporated H3.1 histones very rapidly become monomethylated on lysine 27 by ATRX5 and 6, which are thought to travel with the replication fork 115 ; this restricts TSK binding and thus Polθ recruitment, thereby avoiding the duplication of heterochromatic sequences 117 . ...

The histone H3.1 variant regulates TONSOKU-mediated DNA repair during replication
  • Citing Article
  • March 2022

Science

... Nanomaterials possess unique physicochemical properties and biocompatibility, allowing them to be designed and prepared as carriers or delivery systems with specific functions for delivering cGAS or STING inhibitors to regulate the cGAS-STING signaling pathway [64,65]. Nanomaterial technology also holds potential for applications in treating myocardial infarction (MI), especially by modulating immune responses to alleviate myocardial damage and promote repair [66][67][68][69]. ...

Nanoengineered Sprayable Therapy for Treating Myocardial Infarction

ACS Nano

... Biofilm is a matrix made of extracellular polymeric substances (EPS) where the bacterial colonies are embedded. Biofilm formation by bacteria facilitates their root colonization and boosts the root-microbe interaction (18). Previous findings indicate that flavonoids, apigenin and luteolin, serve as potent inducers of biofilm formation in diazotrophic bacteria (6). ...

Mimicking biofilm formation and development: Recent progress in In Vitro and In Vivo biofilm models

iScience

... Nanoparticle pellets were obtained and added to a 0.5% agarose gel solution (1:2; nanoparticle: gel) via thorough pipette mixing. In general, nanoparticles may continue to grow for 24 h after synthesis, and those with less stable capping agents may continue to grow slowly after 24 h [22]. To ensure reproducibility and smaller size, our nanoparticles were combined with the gel within an hour of nanoparticle synthesis. ...

A low cost and open access system for rapid synthesis of large volumes of gold and silver nanoparticles

... In order to create colored cornea replacements with incorporated SNPs that have antibacterial qualities, Alarcon et al. designed a unique technique. [204] In cultivation of corneal epithelial cells, the authors previously discovered that encapsulating SNPs with collagen kept their antimicrobial effects; nevertheless, this procedure resulted in a bright yellow tint. [205] SNPs cannot be used for bandage contact lenses or corneal repairs because of this discoloration. ...

Coloured cornea replacements with anti-infective properties: Expanding the safe use of silver nanoparticles in regenerative medicine
  • Citing Article
  • March 2016

Nanoscale