Alginate Dressings Continuously for 14 Days on Uncontaminated, Superficial, Partial Thickness Burns.

Calcium alginate dressings are commonly used on split-thickness skin donor sites, where they are typically removed after 14 days. Alginates have been used previously on superficial, partial thickness burns, but changed every 3 to 5 days. In this study, alginates were applied to superficial, partial thickness burns on adults within 36 hours of injury, then left intact for up to 14 days. Wound healing (≥95% wound epithelialization) and pain were measured. Twenty-one burns were reviewed on ten patients. Per the initial protocol, six patients were reviewed every 3 to 5 days, with removal of only secondary dressings, until days 13 to 14, when the alginate dressings were removed. One patient was reviewed every 3 to 5 days until day 10, when a clinic nurse removed the alginate dressing. Restrictions on movement during the COVID pandemic necessitated a protocol change, with only one review at approximately day 14 for removal of alginate and secondary dressings; three patients were reviewed in this manner. Burns on all patients were 100% epithelialized at the time of final review and there were no complications, such as scarring, infection, or need for grafting. Following initial debridement and dressings, patients reported minimal pain. Dressing costs appeared to be significantly decreased. This protocol may be particularly useful for patients managed in rural and remote locations, with telemedicine support if required.

Thiol surface functionalization via continuous phase plasma polymerization of allyl mercaptan, with subsequent maleimide-linked conjugation of collagen.

Thiol groups can undergo a large variety of chemical reactions and are used in solution phase to conjugate many bioactive molecules. Previous research on solid substrates with continuous phase glow discharge polymerization of thiol-containing monomers may have been compromised by oxidation. Thiol surface functionalization via glow discharge polymerization has been reported as requiring pulsing. Herein, continuous phase glow discharge polymerization of allyl mercaptan (2-propene-1-thiol) was used to generate significant densities of thiol groups on a mixed macrodiol polyurethane and tantalum. Three general classes of chemistry are used to conjugate proteins to thiol groups, with maleimide linkers being used most commonly. Here the pH specificity of maleimide reactions was used effectively to conjugate surface-bound thiol groups to amine groups in collagen. XPS demonstrated surface-bound thiol groups without evidence of oxidation, along with the subsequent presence of maleimide and collagen. Glow discharge reactor parameters were optimized by testing the resistance of bound collagen to degradation by 8 M urea. The nature of the chemical bonding of collagen to surface thiol groups was effectively assessed by colorimetric assay (ELISA) of residual collagen after incubation in 8 M urea over 8 days and after incubation with keratinocytes over 15 days. The facile creation of useable solid-supported thiol groups via continuous phase glow discharge polymerization of allyl mercaptan opens a route for attaching a vast array of bioactive molecules. © 2016 Wiley Periodicals, Inc. J Biomed Mater Res Part A: 105A: 1940-1948, 2017.

Surface-bound collagen 4 is significantly more stable than collagen 1.

Collagen 1 (C1) is commonly used to improve biological responses to implant surfaces. Here, the stability of C1 was compared with collagen 4 (C4) on a mixed macrodiol polyurethane, both adsorbed and covalently bound via acetaldehyde glow discharge polymerization and reductive amination. Substrate specimens were incubated in solutions of C1 and C4. The strength of conjugation was tested by incubation in 8 M urea followed by enzyme linked immunosorbent assays to measure residual C1 and C4. The basal lamina protein, laminin-332 (L332) was superimposed via adsorption on C4-treated specimens. Keratinocytes were grown on untreated, C1-treated, C4-treated, and C4 + L332-treated specimens, followed by measurement of cell area, proliferation, and focal adhesion density. Adsorbed C4 was shown to be significantly more stable than C1 and covalent conjugation conferred even greater stability, with no degradation of C4 over twenty days in 8 M urea. Cell growth was similar for C1 and C4, with no additional benefit conferred by superimposition of L332. The greater resistance of C4 to degradation may be consequent to cysteine residues and disulphide bonds in its non-collagenous domains. The use of C4 on implants, rather than C1, may improve their long-term stability in tissues. © 2017 Wiley Periodicals, Inc. J Biomed Mater Res Part A: 105A: 1364-1373, 2017.

Toward a skin-material interface with vacuum-integrated capped macroporous scaffolds.

Avulsion, epidermal marsupialization, and infection cause failure at the skin-material interface. A robust interface would permit implantable robotics, prosthetics, and other medical devices; reconstruction of surgical defects, and long-term access to blood vessels and body cavities. Torus-shaped cap-scaffold structures were designed to work in conjunction with negative pressure to address the three causes of failure. Six wounds were made on the backs of each of four 3-month old pigs. Four unmodified (no caps) scaffolds were implanted along with 20 cap-scaffolds. Collagen type 4 was attached to 21 implants. Negative pressure then was applied. Structures were explanted and assessed histologically at day 7 and day 28. At day 28, there was close tissue apposition to scaffolds, without detectable reactions from defensive or interfering cells. Three cap-scaffolds explanted at day 28 showed likely attachment of epidermis to the cap or cap-scaffold junction, without deeper marsupialization. The combination of toric-shaped cap-scaffolds with negative pressure appears to be an intrinsically biocompatible system, enabling a robust skin-material interface. © 2016 Wiley Periodicals, Inc. J Biomed Mater Res Part B: Appl Biomater, 105B: 1307-1318, 2017.

Tissue compatibility of biomaterials: benefits and problems of skin biointegration.

The integration of biomaterials with skin is necessary to enable infection-free access to vasculature and body cavities. Also, integrating plastics and metals with skin increases options for the reconstruction of surgical and traumatic defects and enables the permanent implantation of robotic and electronic devices. Until now, attempts to integrate biomaterials with skin permanently have failed because of epidermal marsupialization and infection. This article reviews the general properties required of biomaterials to optimize integration with body tissues, the modifications that increase biocompatibility, focusing particularly on surface functionalization and the specific requirements for biomaterial integration into skin. Critical pathophysiological processes relating to biocompatibility are discussed with particular emphasis on the skin-biomaterial interface. Future directions are speculated on, in particular, the specific utility of subatmospheric pressure dressings in facilitating tissue integration into biomaterials.