The goal of this research project is to create a Mathcad template file capable of statistically modelling the effects of mean and standard deviation on a microparticle batch characterized by the log normal distribution model. Such a file can be applied during manufacturing to explore tolerances and increase cost and time effectiveness. Theoretical data for the time to 60% drug release and the slope and intercept of the log-log plot were collected and subjected to statistical analysis in JMP. Since the scope of this project focuses on microparticle surface degradation drug release with no drug diffusion, the characteristic variables relating to the slope (n = diffusional release exponent) and the intercept (k = kinetic constant) do not directly apply to the distribution model within the scope of the research. However, these variables are useful for analysis when the Mathcad template is applied to other types of drug release models.

Polymeric nanoparticles (NP) consisting of Poly Lactic-co-lactic acid - methyl polyethylene glycol (PLLA-mPEG) or Poly Lactic-co-Glycolic Acid (PLGA) are an emerging field of study for therapeutic and diagnostic applications. NPs have a variety of tunable physical characteristics like size, morphology, and surface topography. They can be loaded with therapeutic and/or diagnostic agents, either on the surface or within the core. NP size is an important characteristic as it directly impacts clearance and where the particles can travel and bind in the body. To that end, the typical target size for NPs is 30-200 nm for the majority of applications. Fabricating NPs using the typical techniques such as drop emulsion, microfluidics, or traditional nanoprecipitation can be expensive and may not yield the appropriate particle size. Therefore, a need has emerged for low-cost fabrication methods that allow customization of NP physical characteristics with high reproducibility. In this study we manufactured a low-cost (<$210), open-source syringe pump that can be used in nanoprecipitation. A design of experiments was utilized to find the relationship between the independent variables: polymer concentration (mg/mL), agitation rate of aqueous solution (rpm), and injection rate of the polymer solution (mL/min) and the dependent variables: size (nm), zeta potential, and polydispersity index (PDI). The quarter factorial design consisted of 4 experiments, each of which was manufactured in batches of three. Each sample of each batch was measured three times via dynamic light scattering. The particles were made with PLLA-mPEG dissolved in a 50% dichloromethane and 50% acetone solution. The polymer solution was dispensed into the aqueous solution containing 0.3% polyvinyl alcohol (PVA). Data suggests that none of the factors had a statistically significant effect on NP size. However, all interactions and relationships showed that there was a negative correlation between the above defined input parameters and the NP size. The NP sizes ranged from 276.144 ± 14.710 nm at the largest to 185.611 ± 15.634 nm at the smallest. In conclusion, the low-cost syringe pump nanoprecipitation method can achieve small sizes like the ones reported with drop emulsion or microfluidics. While there are trends suggesting predictable tuning of physical characteristics, significant control over the customization has not yet been achieved.

The current clinical gold standards for tissue sealing include sutures, staples, and glues, however several adverse effects limit their use. Sutures and staples inherently cause additional trauma to tissue surrounding the wound, and glues can be lacking in adhesion and are potentially inflammatory. All three also introduce risk of infection. Light-activated tissue sealing, particularly the use of near-infrared light, is an attractive alternative, as it localizes heat, thereby preventing thermal damage to the surrounding healthy tissue. Previous work identified a glutaraldehyde-crosslinked chitosan film as a lead sealant for gastrointestinal incision sealing, but in vivo testing resulted in tissue degradation in and around the wound. The suggested causes for this degradation were excess acetic acid, endotoxins in the chitosan, and thermal damage. A basic buffer wash protocol was developed to remove excess acid from the films following fabrication. UV-Vis spectroscopy demonstrated that following the wash, films had the same concentration of Indocyanine green as unwashed films, allowing them to absorb light at the same wavelength, therefore showing the wash did not affect the film’s function. However subsequent washes led to degradation of film mass of nearly 20%. Standard chitosan films had significantly greater mass gain (p = 0.028) and significantly less subsequent loss (p= 0.012) than endotoxin free chitosan-films after soaking in phosphate buffered saline for varying durations , while soaking duration had no effect (p = 0.332). Leak pressure testing of films prepared with varying numbers of buffer washes, laser temperature, and lasering time revealed no significant interaction between any of the 3 variables. As such, it was confirmed that proceeding with in vivo testing with the buffer wash, various lasering temperatures, and laser times would not affect the sealing performance of the films. Future investigation will involve characterization of additional materials that may be effective for sealing of internal wounds, as well as drug loading of agents that may hasten the healing process.