Colorimetric Hydrogel Based Nanosensor for Detection of Therapeutic Levels of Ionizing Radiation

Abstract

An apparatus includes a hydrogel including a metallic compound, a surfactant, an acid, agarose and water. The hydrogel is substantially colorless. A radiated hydrogel having a color is formed when the hydrogel receives a low dose of ionizing radiation.

Description

FIELD

This disclosure relates to nanosensors and more particularly to hydrogel nanosensors for measuring therapeutic levels of ionizing radiation.

BACKGROUND

Radiation therapy is a common primary treatment modality for multiple malignancies, including cancers of the head and neck, breast, lung, prostate, and rectum. Depending on the disease, radiation doses ranging from 20 to 70 Gy are often employed for therapeutic use. Diseased tissue and normal organ radiation sensitivities also vary. In order to maximize disease treatment relative to radiation-induced side-effects, various methods of delivery including hyperfractionation (0.5-1.8 Gy), conventional fractionation (1.8-2.2 Gy), and hypofractionation (3-10 Gy) have been explored. These delivery methods explore different regimes of radiation sensitivity in order to maximize tumor cell killing while optimizing treatment times.

Despite obvious advantages with radiotherapy, there can be significant radiation-induced toxicity in tissues. For example, radiation-induced proctitis can be a significant morbidity for patients undergoing prostate or endometrial cancer treatment. For centrally located lung cancer radiotherapy, the esophagus can be incidentally irradiated during treatments, resulting in esophagitis. In the head and neck, radiation of salivary gland or pharyngeal tumors can induce radiation-induced osteonecrosis. Another concern during radiotherapy is the motion of the patient as well as the natural peristalsis of internal organs. These issues highlight the importance of appropriately dosing the cancerous tumors while sparing the normal tissue in order to prevent significant morbidity that arises from radiation toxicity.

Despite several transformative advances since its inception in the late 19^th century, radiation therapy is a complex process aimed at maximizing the dose delivered to the tumor environments while sparing normal tissue of unnecessary radiation. This has led to the development of image-guided and intensity modulated radiation therapy. The process of treatment planning requires initial simulation followed by verification of dose delivery with anthropomorphic phantoms which simulate human tissue with more or less homogeneous, polymeric materials. The accuracy of the planning is measured using either anthropomorphic phantom or 3D dosimeters. During the treatment, actual dose delivery can be verified with a combination of entry, exit or luminal dose measurements. Administered in vivo doses can be measured with diodes (surface or implantable), thermoluminescent detectors (TLDs), or other scintillating detectors. However, these detectors are either invasive, difficult to handle (due to fragility or sensitivity to heat and light), require separate read-out device, or measure surface doses only. TLDs are typically laborious to operate and require repeated calibration while diodes suffer from angular, energy and dose rate dependent responses. Although MOSFETs can overcome some of these limitations, they typically require highly stable power supplies. In addition, these dosimeters require sophisticated and therefore, expensive, fabrication processes in many cases. In light of these drawbacks, there is still a need for the development of robust and simple sensors in order to assist or replace existing dosimeters that can be employed during sessions of fractionated radiotherapy.

Radiotherapy along with chemotherapy are still the widely accepted treatment options for cancerous diseases. Over the past twenty years, radiotherapy has undergone major changes including image guided delivery, intensity-modulated radiation therapy (IMIRT), Stereotactic radiosurgery (SRS) and Stereotactic body radiotherapy (SBRT). Along with advancement of sophisticated radiotherapy techniques, the complexity of such procedures has drastically increased. The complex planning process involves numerous individuals enhancing the probability of human error being committed and leading to disturbing outcomes in patient morbidity. One potential solution to avoid such errors is the use of dosimeters to measure and confirm the radiation dose being delivered. Current dosimeters including semiconductor diodes, MOSFETs and Thermoluminescent dosimeters are 1D dosimeters wherein they do not have the capability of rendering a 2D response. To overcome this disadvantage and register spatial dose information led to the development of polymer gel dosimeters. These gel based dosimeters find application during IMRT and SRS treatments. Despite the advantages which warrant their everyday use, these dosimeters are rarely ever used. The biggest limitation preventing their day to day use is the use of Magnetic resonance imaging (MRI) to read the gels which requires highly skilled professionals to perform day to day measurements. For accurate readouts, longer time scans are required which would proportionally increase the cost. In addition, they require complex synthesis protocols including preparation in a fume hood and evacuation of air to prevent oxygen diffusion into the gel. These limitations of the polymer based gel dosimeters make their use highly unlikely on a frequent basis. Taking these into consideration, there is still a requirement for the development of a simple dosimeter which can render spatial information which can be read easily.

SUMMARY

This disclosure describes lipid-templated formation of colored dispersions of gold nanoparticles from colorless metal salts as a facile, visual and colorimetric indicator of therapeutic levels of ionizing radiation (X-rays), leading to applications in radiation dosimetry. The current nanosensor can detect radiation doses as low as 0.5 Gy, and exhibit a linear response for doses relevant in therapeutic administration of radiation (0.5-2 Gy). Modulating the concentration and chemistry of the templating lipid results in linear response in different dose ranges, indicating the versatility of the current plasmonic nanosensor platform.

This disclosure also describes a hydrogel-based sensor for detection of low doses of ionizing radiation. The sensor works on the principle of a color change which reports for the radiation dose employed. Ionizing radiation induced conversion of colorless salt solutions of univalent gold ions (Au1) to maroon-colored dispersions of plasmonic gold nanoparticles were used as reporters for ionizing radiation. The color change is qualitatively observed by the naked eye and quantitative measurements are made using a UV-Vis spectrophotometer. The ability of this sensor to measure therapeutic levels of radiation, combined with its facile synthesis make it a viable dosimeter during radiotherapy, military and other applications where reporters of low doses of radiation is required.

In summary, the disclosure describes the detection of ionizing radiation through a hydrogel based nanosensor. The hydrogel based sensor changes color upon exposure to ionizing radiation. The intensity of the color varies with the exposed dose and is used to report for the irradiation conditions. Being encapsulated in a hydrogel, makes the sensor render spatial information regarding the points where irradiation has occurred.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a schematic (Adapted from Perez-Juste, J.; Liz-Marzán, L. M.; Carnie, S.; Chan, D. Y. C.; Mulvaney, P., Electric-Field-Directed Growth of Gold Nanorods in Aqueous Surfactant Solutions. Advanced Functional Materials 2004, 14 (6), 571-579.) depicting the reaction progress after addition of various components in the plasmonic nanosensor for ionizing radiation.

FIGS. 2A-2C show a UV-Vis absorption spectra of the control (0 Gy), irradiated samples containing (FIG. 2A) C₁₆TAB, (FIG. 2B) C₁₂TAB and (FIG. 2C) C₈TAB after 7 hours.

FIGS. 3A-3E show optical images of samples containing different C₁₆TAB and C₁₂TAB concentrations irradiated with a range of X-ray doses (Gy) (FIG. 3A) 2 mM C₁₆TAB, (FIG. 3B) 4 mM C₁₆TAB, (FIG. 3C) 10 mM C₁₆TAB, (FIG. 3D) 20 mM C₁₆TAB and (FIG. 3E) 20 mM C₁₂TAB 2 hours post irradiation.

FIG. 4 shows a graph of maximum absorbance vs. radiation dose for varying concentrations of C₁₆TAB after 2 hours post irradiation—filled diamonds, solid line: 2 mM C₁₆TAB, filled circles, dashed line: 4 mM C₁₆TAB, filled triangles, solid line: 10 mM C₁₆TAB, and filled squares, solid line: 20 mM C₁₆TAB.

FIGS. 5A-5D show Transmission Electron Microscopy (TEM) images of nanoparticles after exposure to ionizing (X-ray) radiation using two different lipid surfactants, 20 mM C₁₆TAB (left) and 20 mM C₁₂TAB (right) for (FIG. 5A) 1 Gy, (FIG. 5B) 47 Gy, (FIG. 5C) 5 Gy and (FIG. 5D) 47 Gy.

FIGS. 6A-6B show (FIG. 6A) an endorectal balloon with precursor solution before irradiation with X-rays and (FIG. 6B) endorectal balloon post irradiation with 10.5 Gy X-rays.

FIGS. 7A-7B show (FIG. 7A) digital image showing the nanoscale precursor solution (200 μL) in microcentrifuge tubes placed along the stem outside of an endorectal balloon and (FIG. 7B) X-Ray contrast image of the phantom which shows the dose treatment plan, prostate tissue, the endorectal balloon, and the microcentrifuge tube/nanosensor location below the prostate tissue and on the endorectal balloon.

FIG. 8 shows an illustration of a composition of matter including a hydrogel.

FIG. 9 shows a flow diagram of a method for forming a substantially colorless shaped-hydrogel.

FIG. 10 shows a block diagram of an apparatus including a substantially colorless hydrogel to receive a low dose of radiation and form a radiated hydrogel having a color, and a detector optically coupled to the radiated hydrogel.

FIGS. 11A-11D show UV-Visible spectral profiles of (FIG. 11A) HAuCl₄, (FIG. 11B) HAuCl₄ (0.196 mM)+C₁₆TAB (20 mM), (FIG. 11C) HAuCl₄ (0.196 mM)+C₁₆TAB (20 mM)+Ascorbic Acid (5.88 mM) and (FIG. 11D) HAuCl₄ (0.196 mM)+Ascorbic Acid (5.88 mM)AA).

FIGS. 12A-12B show (FIG. 12A) UV-Vis spectra of varying ascorbic acid volumes along with gold and C₁₆TAB irradiated at 47 Gy including a significant increase in the absorbance peak intensity is observed at ˜520 nm when the amount of ascorbic acid is increased, indicating an increase in the formation of gold nanoparticles and (FIG. 12B) maximum absorbance values of samples containing varying concentrations of ascorbic acid denoted as [AA].

FIGS. 13A-13C show absorbance spectra of (FIG. 13A) gold salt (0.196 mM) (FIG. 13B) gold salt (0.196 mM)+C₁₆TAB (20 mM) (FIG. 13C) gold salt (0.196 mM)+C₁₂TAB (20 mM).

FIGS. 14A-14C show kinetics of gold nanoparticle formation following exposure to different doses of ionizing radiation (0-47 Gy) for (FIG. 14A) C₁₆TAB, (FIG. 14B) C₁₂TAB and (FIG. 14C) C₈TAB.

FIG. 15 shows maximum absorbance vs. radiation dose (Gy) after 2 hours of X-ray irradiation with C₁₆TAB (filled squares, solid line) and C₁₂TAB (open circles, dotted line) surfactants.

FIG. 16 shows intensity ratio of I337/I334 as a function of surfactant concentration as used to determine the critical micellar concentration.

FIGS. 17A-17C show absorbance spectra of precursor monovalent gold salt solutions under conditions of no radiation (i.e. 0 Gy) in presence of different concentrations of (FIG. 17A) C₁₆TAB and (FIG. 17B) C₁₂TAB and (FIG. 17C) C₈TAB recorded after 10 minutes of incubation.

FIGS. 18A-18D show Maximum Absorbance vs. Wavelength for different concentrations of C₁₆TAB after a duration of 2 hours post irradiation (FIG. 18A) 2 mM (FIG. 18B) 4 mM (FIG. 18C) 10 mM (FIG. 18D) 20 mM.

FIGS. 19A-19B show (FIG. 19A) Hydrodynamic diameter vs. radiation dose and (FIG. 19B) Hydrodynamic diameter vs. radiation dose (plotted on a log₁₀ on the X-axis).

FIGS. 20A-20D show transmission electron microscopy (TEM) images of anisotropic nanostructures (FIG. 20A) dendritic and (FIG. 20C) nanowire-like structures formed in case of C₁₂TAB at 5 Gy X-ray radiation dose and images (FIG. 20B) and (FIG. 20D) show magnified images of the highlighted regions inside the box from Fig. (FIG. 20A) and (FIG. 20C).

FIGS. 21A-21G show Transmission Electron Microscopy (TEM) images of nanoparticles formed after exposure to ionizing (X-ray) radiation using the following conditions of C₁₆TAB: (FIG. 21A) 10 mM and 5 Gy, (FIG. 21B) 10 mM and 47 Gy, (FIG. 21C) 4 mM and 5 Gy, (FIG. 21D) 4 mM and 15 Gy, (FIG. 21E) 2 mM and 0.5 Gy, (FIG. 21F) magnified image of highlighted area of E, and (FIG. 21G) 2 mM and 2.5 Gy.

FIG. 22A shows a digital image of a phantom.

FIG. 22B show a digital image of the phantom irradiation set-up including the phantom shown in FIG. 22A on the linear accelerator at Banner MD Anderson.

FIG. 23 shows a schematic diagram representing the fabrication of the hydrogel sensors for the detection of ionizing radiation—a mixture of HAuCl₄ and C_xTAB is mixed with liquid agarose and allowed to set in a circular mold, prior to radiation treatment ascorbic acid is allowed to diffuse into the gel from the top for 10 minutes, and this results in the formation of a colorless hydrogel and irradiation with high energy photons results in the formation of gold nanoparticles in the hydrogel along the region of irradiation.

FIG. 24 shows optical images of the hydrogel containing C₁₆TAB (Top) and C₁₂TAB (Bottom) after t=1 hr with the irradiated doses indicated below each image.

FIG. 25 shows Maximum absorbance vs Radiation dose post X-ray irradiation after t=1 hr with solid line representing (CuTAB) and dashed line representing C₁₆TAB.

FIG. 26A show kinetics of gold nanoparticle formation following X-ray irradiation with a dose of C₁₂TAB and the absorbance value reaching a steady state at t=1 hr and remaining stable over a period of 4 hours

FIG. 26B shows kinetics of gold nanoparticle formation following X-ray irradiation with a dose of C₁₆TAB and the absorbance value reaching a steady state at t=1 hr and remaining stable over a period of 4 hours.

FIGS. 27A-27B (FIG. 27A) shows maximum absorbance of the hydrogels irradiated with 2 Gy with different dose rates and energy (6 MV and 15 MV) with no significant differences in absorbance observed at the above conditions and (FIG. 27B) ion chamber measurements to determine ionizing radiation attenuation with presence of heavy metal (Au) leading to minimal (not significant) dose attenuation with the ion chamber below the gel measuring the radiation that passes through the hydrogel.

FIG. 28 shows an X-Ray contrast image of the phantom displaying the treatment plan (Left) and the optical images of the gel exposed under different irradiation conditions (Right) after t=2 hour.

FIG. 29 shows addition of Na₂S prevents diffusion of the nanoparticles from the irradiated region to the un-irradiated one.

FIG. 30 shows time lapse images of formation of opaque pink regions irradiated in the hydrogel resulting in ASU logo at the end of three minutes.

DESCRIPTION

Facile radiation sensors have the potential to transform methods and planning in clinical radiotherapy. Below are described results of studies on a colorimetric, liquid-phase nanosensor that can detect therapeutic levels of ionizing radiation. X-rays, in concert with templating lipid micelles, were employed to induce the formation of colored dispersions of gold nanoparticles from corresponding metal salts, resulting in a easy to use visible indicator of ionizing radiation.

The novel plasmonic nanosensor employs a colorless metal salt solution comprising a mixture of auric chloride (HAuCl₄), L-Ascorbic acid (AA) and cetyl (C₁₆), dodecyl (C₁₂), or octyl (C₈) trimethylammonium bromide (C_{x; x=16/12/8}TAB) surfactant molecules (FIG. 1; please see the Experimental Section for more details). In brief, C_xTAB and HAuCl₄ were first mixed leading to the formation of A^IIIBr₄⁻. HAuCl₄ shows a prominent peak at 340 nm which shifts to 400 nm after addition of C₁₆TAB, likely due to the exchange of a weaker chloride ion by a stronger bromide ion (FIGS. 11A-11B). The shift in absorption peak can also be seen visually as a color change from yellow to orange. Subsequent addition of ascorbic acid turns the solution colorless with no observable peaks between 300 and 999 nm (FIG. 11C). Ascorbic acid reduces Au(III) to Au(I) in a two-electron, step-reduction reaction. It has been shown that addition of up to 5 molar equivalent excess ascorbic acid does not result in the formation of zerovalent gold or Au(0) species, which can be partly attributed to the lower oxidation potential of the acid in presence of C₁₆TAB. This mixture of C_xTAB, ascorbic acid, and HAuCl₄ is employed as the precursor solution for radiation sensing. However, a characteristic peak in the range of 500-600 nm corresponding to gold nanoparticles is observed if ascorbic acid directly reacts with the gold salt in the absence of C₁₆TAB (FIG. 11D), indicating spontaneous formation of nanoparticles in absence of the surfactant under the conditions employed.

First, attempts were made to convert trivalent gold to its univalent state, since the reduction of Au(I) to Au(0) is thermodynamically favored over the reduction of Au(III) to Au(0), due to a higher standard reduction potential of the former. Au(I) has an electronic configuration of 4f¹⁴5d¹⁰, and requires a single electron for conversion (reduction) to Au(0). This formation of zerovalent gold or Au(0) is a prerequisite step for nanoparticle formation. In the current plasmonic nanosensor, the electron transfer required for converting Au(I) to Au(0) is facilitated by splitting water into free radicals following exposure to ionizing radiation (X-rays). Water splitting by ionizing radiation generates three key free radicals, two of which, e⁻ and H., are reducing, and the other OR) oxidizing in nature. Excess ascorbic acid is an antioxidant capable of removing the detrimental (oxidizing) OR radicals generated in the system. C_xTAB surfactants were employed due for their ability to template gold nanoparticles. These three species, namely ascorbic acid, C_xTAB, and gold salt, form the key constituents of the current plasmonic nanosensor for ionizing radiation.

First, the concentration of ascorbic acid (AA) was optimized in the presence of the surfactant (C₁₆TAB) and gold salt employed in the plasmonic nanosensor; the maximal dose of 47 Gy was delivered in order to study the effect of ascorbic acid on nanoparticle formation (FIGS. 12A-12B). A marked increase in nanoparticle formation is observed when excess AA is used and it reaches saturation when 600 μL of 0.01 M (4 mM AA) is employed; similar levels of nanoparticle formation are seen when 900 μL of 0.01 M (5.88 mM AA) are employed. Although saturation was observed when 600 μL of AA were used, 5.88 mM AA was used for all subsequent experiments in order to ensure adequate quenching of the detrimental OH. radicals which otherwise adversely affects the yield of nanoparticles generated. Control experiments with (1) gold salt (HAuCl₄) alone, (2) gold salt+C₁₆TAB and (3) gold salt+C₁₂TAB were also carried out in presence of different X-ray doses, but in absence of ascorbic acid. Absorbance profiles of the samples were measured after 7 hours and the absence of peaks from 500-900 nm indicated the absence of plasmonic (gold) nanoparticles (FIGS. 13A-13C).

Next, the efficacy of three cationic surfactants, C₈TAB C₁₂TAB, and C₁₆TAB was investigated, for inducing nanoparticle formation in presence of different doses of ionizing radiation (FIGS. 2A-2C). All three surfactants have trimethyl ammonium moieties as the head group and bromide as the counter ions; only the lipid chain length was varied as C₈, C₁₂, and C₁₆ in these molecules. As stated previously, a large number of e⁻_aq and H. radicals are generated following exposure of the solution to X-rays which facilitate the conversion of Au⁺ ions to their zerovalent Au⁰ state. The Au⁰ species act as seeds upon which further nucleation and coalescence occurs. This, in turn, leads to an increase in size and eventual formation of nanoparticles, which are stabilized by surfactant molecules. Formation of these plasmonic nanoparticles imparts a burgundy/maroon color to the dispersion; the intensity of the color increases with an increase in radiation dose applied (FIGS. 3A-3E).

Nanoparticle formation was seen as early as 1 h following irradiation in many cases, although 2 h were required for samples irradiated with lower doses (1, 3 and 5 Gy) (FIGS. 14A-14C). No significant differences in absorbance intensity were observed thereafter until a period of 7 hours, which was the maximum duration investigated in these cases. Nanoparticle formation was observed at radiation doses as low as 1 Gy, which is well within the range of doses employed for radiotherapy. While C₁₆TAB or C₁₂TAB were effective at templating nanoparticle formation even at low doses (1-5 Gy), C₈TAB did not show any propensity for templating nanoparticle formation even at the highest radiation dose (47 Gy) employed. C₁₂TAB-templated gold nanoparticles exhibited unique spectral profiles under ionizing radiation; two spectral peaks—one between 500 and 550 nm and another between 650 and 800 nm—were seen (FIG. 2B). This is in contrast to C₁₆TAB which exhibited only a single peak between 500 and 600 nm (FIG. 2A). Finally, the linear response for C₁₆TAB was significantly more pronounced than that for C₁₂TAB (FIG. 15).

The critical micelle concentration (CMC) of C₁₆TAB is reported to be approximately 1 mM. Using the pyrene fluorescence assay, we determined the CMC of C₁₆TAB in the nanosensor precursor solution (i.e. gold salt and ascorbic acid in water) to be ˜0.7±0.1 mM, which is slightly lower than ˜1.2±0.02 mM in THIS solvent (FIG. 16). Pre-micellar aggregates are thought to exist when C₁₆TAB concentration is lower than 7.4 mM, while stable micelles are observed at higher concentrations of the lipid surfactant. One hypothesis is that increasing the ratio of the metallic species (Au⁺) to the aggregate (pre-micellar/micellar) C₁₆TAB species would lead to greater propensity for nanoparticle formation upon exposure to ionizing radiation and therefore increased sensitivity of the resulting nanosensor at lower radiation doses. Based on the hypothesis that the number of aggregate species increases with lipid concentration, lower concentrations of C₁₆TAB (2 mM, 4 mM and 10 mM) was investigated, while keeping the gold and ascorbic acid concentration constant.

Use of C₁₆TAB concentrations at and below the CMC (i.e. 0.7 and 0.2 mM) resulted in spontaneous formation of gold nanoparticles in absence of ionizing radiation; gold nanoparticle formation can be seen by the characteristic absorbance peak of the dispersion in FIGS. 17A-17C. However, the propensity for spontaneous nanoparticle is significantly reduced or lost at concentrations above the CMC. A distinct color change can be observed for radiation doses as low as 0.5 Gy for the lowest concentration of C₁₆TAB above the CMC investigated (FIGS. 3A and 19A-19B). A linear response was observed for radiation doses ranging from 0.5 to 2 Gy under these conditions (FIGS. 5A-5D). As the concentration of C₁₆TAB increases, the radiation dose required to template nanoparticle formation also increases (FIGS. 4 and 18A-18D). Furthermore, the color of the nanoparticle dispersion formed is significantly different in cases of 2 mM (blue-violet) C₁₆TAB compared to that observed in cases of 4 mM (bluish-red), 10 mM (red/pink) and 20 mM (burgundy/maroon) C₁₆TAB, indicating different sizes of nanoparticles under these conditions. While it is most desired that the nanosensor is sensitive to therapeutic doses used in conventional and hyperfractionated radiotherapy (˜0.5-2.2 Gy), these results indicate that the response of the plasmonic nanosensor can be tuned by simply modifying the concentration of the lipid surfactant.

Visual colorimetric sensors possess advantages of convenience and likely, cost, over those that employ fluorescence changes or electron spin resonance measurements for detecting ionizing radiation. The current plasmonic nanosensor shows increasing color intensity with increasing radiation dose (FIGS. 2A-2C and 3A-3E). The increase in color intensity with radiation dose is reflected in an increase in maximures 2 al (peak) absorbance values, which in turn, are surrogates for the concentrations of nanoparticles formed in the dispersion. Key features of gold nanoparticle absorbance spectra include the shape of the surface plasmon resonance band and the position of the maximal (peak) absorption wavelength. The width of the spectral profiles at lower doses signifies a somewhat polydisperse population of the nanoparticles (FIGS. 2A, 2B and FIG. 18A-18D). The absorbance peaks are red-shifted with decreasing radiation doses, suggesting an increase in particle size under these conditions compared to those obtained at higher doses.

Free radicals generated upon radiolysis are thought to be localized in finite volumes called spurs. These spurs can expand, diffuse, and simultaneously, react, leading to the formation of molecular products. These highly reactive free radicals have very short lifetimes of ˜10⁻⁷-10⁻⁶ at 25° C. Reaction volumes consisting of nanoscale features can facilitate enhanced reaction kinetics and ensure efficient utilization of these free radicals for the formation of nanoparticles. In case of the current plasmonic nanosensor, this was achieved by the use of amphiphilic molecules that self-assemble into micelles above their respective critical micellar concentrations (CMCs). A strong interaction is possible between the positively charged head group of the lipid surfactant micelles and the negatively charged AuCl₄⁻ ions (FIG. 1). This interaction can lead to incorporation of AuCl₄⁻ ions in the water-rich Stern layer leading to the formation of a ‘nanoreactor’. However, spontaneous formation of nanoparticles (i.e. in absence of ionizing radiation) was seen when concentrations of C₁₆TAB were lower than the CMC (FIGS. 17A-17C). One hypothesis is that spontaneous nanoparticle formation observed at lower concentrations of the surfactant is likely due to negligible steric hindrance between the surfactant and ascorbic acid; absence of these barriers results in nanoparticle growth which can be spectroscopically observed. It is only when the concentrations of C₁₂TAB and C₁₆TAB are higher than the CMC, that no spontaneous formation of gold nanoparticles is seen, and ionizing radiation is required to induce nanoparticle formation. This, therefore, acts as the functional principle behind the current plasmonic nanosensor. Of the three lipid surfactants, only the concentration of C₈TAB was significantly below its CMC value (130 mM), while the concentrations employed were significantly higher than the CMCs of C₁₂TAB (CMC=15 mM) and C₁₆TAB (CMC=1 mM). In the case of C₈TAB, there is an absence of these “nanoreactors”, which may explain lack of nanoparticle formation under these conditions. These observations suggest that interplay between surfactant chemistry and aggregation state determine nanoparticle formation by lipid-based surfactant molecules.

Nanoparticles formed in presence and absence of ionizing radiation were characterized for their morphology and hydrodynamic diameter using transmission electron microscopy (TEM; FIGS. 5A-5D, and FIGS. 20A-20D and 21A-21G) and dynamic light scattering (FIGS. 19A-19B), respectively. While C₁₆TAB-templated nanoparticles showed a single maximal absorption peak (at ca. 520 nm), C₁₂TAB-templated nanoparticles showed two peaks: one at ca. 520 nm (visual region) and another at ca. 700 nm (near infrared or NIR region; FIG. 2B), particularly at higher doses of ionizing radiation. TEM images indicated that a mixture of spherical and rod-shaped nanoparticles was observed at the higher radiation doses (47 Gy) in case of C₁₂TAB as the templating surfactant (FIG. 5D). This explains the absorption spectral profile with peaks in both, the visual and near infrared range of the spectrum in case of nanoparticles templated using C₁₂TAB (FIG. 2B). A significant decrease in the near infrared absorption peak is observed at lower X-ray doses. Although the spectral profile indicates formation of gold nanospheres, we observed an ensemble of unique anisotropic (dendritic and nanowire) structures (FIGS. 20A-20D). Such structures were not observed at similar X-ray doses in case of C₁₆TAB as the templating surfactant.

The growth of gold nuclei from zerovalent gold species proceeds through continuous diffusion of unreacted metal ions and smaller seeds onto the growing nanocrystal surface. This, in turn, is governed by electrostatic interactions between the cationic micelle loaded with gold seeds and unreacted metal ions. In this case, it is likely that the gold nanoparticles aggregate more rapidly in situ due to the strong hydrophobic nature of the long of C₁₆TAB chains, leading to the formation of quasi-spherical nanoparticles and not anisotropic nanostructures.

TEM images indicated a reduction in the size of the metal nanoparticles with increasing radiation dose. Dynamic light scattering (DLS) studies on irradiated samples (FIGS. 19A-19B and Table S1) indicated a linear decrease in nanoparticle hydrodynamic diameters with increases in X-ray dose, which is in good agreement with information from TEM images. High radiation doses generate a larger number of free radicals in comparison to lower radiation doses, which can lead to the reaction with and therefore, consumption of a higher number of metal ions. This leads to the formation of a higher concentration of zerovalent gold species in comparison to samples irradiated at lower doses. These unstable Au(0) seeds grow and are eventually capped by the cationic surfactant resulting in smaller sized nanoparticles. In contrast, at lower doses of ionizing radiation, the ratio of concentration of Au(0) to Au(I) is likely smaller. It is possible that unreacted metal ions coalesce with the smaller population of gold seeds and in turn lead to the formation of nanoparticles with larger diameters.

The translational potential of a plasmonic nanosensor for detecting X-ray radiation was investigated under conditions that simulate those employed in human prostate radiotherapy. Endorectal balloons are typically used for holding the prostate in place and for protecting the rectal wall during radiotherapy treatments in humans. The efficacy of the plasmonic nanosensor was evaluated in these balloons ex vivo; no studies on human patients were carried out. 1.5 ml of the precursor solution (C₁₆TAB (20 mM)+AA+HAuCl₄) was incorporated into endorectal balloons as shown in FIG. 6A. The nanosensor precursor solution was subjected to two clinically relevant doses of 7.9 and 10.5 Gy (n=3). The absorbance of the plasmonic nanosensor, which changes color in the balloon itself (e.g. light pink color seen in FIG. 6B for a balloon subjected to a radiation dose of 10.5 Gy) was employed to determine the radiation dose delivered to the balloon. A calibration curve between 5 and 37 Gy from the plot between maximum absorbance and radiation dose after 7 hours was employed to determine the radiation dose delivered. Doses of 8.51±1.73 Gy and 7.85±2.05 Gy were calculated from the calibration curve for 10.5 Gy and 7.9 Gy respectively. Due to the nonlinearity of the curve below 5.3 Gy, the control (0 Gy) showed a value 4.38±0.41 Gy (n=3) when the calibration equation was employed, indicating that the operating region of the plasmonic nanosensor, with a CTAB concentration of 20 mM, is between 5 and 37 Gy and is not reliable for lower doses of radiation for CTAB concentrations of 20 mM (Table 1A).

Based on the above findings in the endorectal balloon, the detection efficacy of the plasmonic nanosensor in a phantom that is employed to simulate prostate radiotherapy treatments was investigated. In these studies, 200 μL of the precursor solution (C₁₆TAB (2 mM)+AA+HAuCl₄) was filled in microcentrifuge tubes, which were then taped to the outside surface of an endorectal balloon such that they were aligned along the stem (FIG. 7A). The lower concentration of C₁₆TAB was used, since this concentration results in detection between 0.5-2 Gy (FIGS. 3A-3E top panel). The prostate phantom, with the endorectal balloon placed under the simulated prostate tissue, was irradiated based on a treatment plan described in the Experimental section and shown in FIGS. 22A-22B and 7B. The prostate itself was irradiated with 1 Gy, while the dose fall off at the end was 0.5 Gy (n=3; FIG. 7B). Thus, two microcentrifuge tubes (capsules 1 and 2) along the stem of the balloon just below the prostate were subjected to 1 Gy, while the third one (capsule 3) outside the balloon was subjected to 0.5 Gy. This set up was employed in order to obtain spatial information on the delivered dose along the rectal wall in the tissue phantom.

Optical images (FIGS. 7A-7B) clearly indicate the formation of violet colored dispersions for capsules 1 and 2, while a dispersion of lighter intensity can be seen in capsule 3. The absorbance of the dispersions were measured 2 h following exposure to radiation, and a calibration curve was employed to estimate the radiation dose as indicated by the radiation sensor. Table 2 shows a comparison of the actual dose delivered and the dose estimated from the calibration of the plasmonic nanosensor. The plasmonic nanosensor indicates that capsules 1 and 2 received doses of 1.20±0.11 Gy and 1.17±0.16 Gy, respectively, while capsule 3 received a dose of 0.49±0.04 Gy (Table 2). These are highly reasonable estimates of the actual doses received by the capsules in the tissue phantom, and can be employed to obtain spatial information on the radiation dose delivered. Taken together, the results indicate the utility of the plasmonic nanosensor in as a simple detection system in simulated clinical settings.

An increasing color intensity with increasing radiation dose was observed in the nanosensor which possesses significant advantages of convenience over other sensors that for example rely on electron spin resonance or fluorescence changes. A developing solution which consisted of Na₂S was added after irradiation of hydrogel. The Na₂S solution was allowed to diffuse into the hydrogel for certain period of time ranging from 5 minutes to 15 minutes. Other time of additions were also studied. The addition of the developing solution gives the hydrogel the ability to record the radiation dose in 3-dimensions thus providing 3D information. This has an added advantage, particularly where dose gradients exist in the treatment plan.

The application discloses an easy to use, versatile and powerful nanoscale platform for dosimetry of therapeutically relevant doses of radiation. This method involves readily available chemicals, is easy to visualize due to the colorimetric nature of detection, and does not need expensive equipment for detection. While a ‘yes/no’ determination may be made by the naked eye, only an absorbance spectrophotometer is required for quantifying the radiation dose. A visible color change also ensures the ease of detecting the radiation dose with the naked eye. It was found that both, C₁₂TAB and C₁₆TAB were able to function as templating molecules in the plasmonic nanosensor at concentrations above their critical micelle concentration (CMC). The sensitivity of the sensor to lower radiation doses is enhanced by modifying the concentration of C₁₆TAB, thus making this a highly versatile platform for a variety of applications. Apart from the surfactants used a list of other potential surfactants which could be employed are listed in the Table S2. The chemicals included in the list along with their derivatives are potential chemicals which could be used along with our sensor in its current form or in any other formulation. The metal ions used is not limited to gold. Any species either metallic or non-metallic can be used along with the sensor in its current form or in any other formulation. To name a few, ions of cobalt, iron, silver could be potential replacement for the proof of concept gold employed. The utility of the plasmonic nanosensor was demonstrated in translational applications; the plasmonic nanosensor was able to detect the delivered radiation dose with satisfactory accuracy when placed in an endorectal balloon ex vivo. In addition, the nanosenor was able to detect doses as low as 0.5 Gy and was able to report on the spatial distribution of radiation dose delivered when investigated using an endorectal balloon placed in a prostate tissue phantom. The translational application of such a dosimeter can help therapists with treatment planning and potentially enhance selectivity and efficacy of treatment. Apart from the medical field, this sensor could be employed where there is a need to detect ionizing radiation directly or indirectly.

Composition of Matter

FIG. 8 shows an illustration of a composition of matter 800 including a hydrogel 802. In some embodiments, the hydrogel 802 includes a metallic compound 804, a surfactant 806, an acid 808, an agarose 810, and water 812. A metallic compound is a compound that contains one or more metal elements. Exemplary metallic compounds 804 suitable for use in connection with the hydrogel 802 include metallic salts. An exemplary metallic salt includes a gold salt. An exemplary gold salt includes a salt of auric chloride (HAuCl₄). A surfactant is a compound that lowers the surface tension (or interfacial tension) between two liquids. Exemplary surfactants 806 suitable for use in connection with the hydrogel 802 include cationic surfactants. An exemplary cationic surfactant includes cetyl trimethylammonium bromide (C₁₆TAB). An acid is a chemical substance whose aqueous solutions are characterized by an ability to react with bases and certain metals to form salts. An exemplary acid 808 suitable for use in connection with the hydrogel 802 includes L-ascorbic acid. The agarose 810 is a linear polymer. In some embodiments the agarose 810 is made up of the repeating unit of agarobiose, which is a disaccharide made up of D-galactose and 3,6-anhydro-L-galactopyranose. In some embodiments, the hydrogel 802 is substantially colorless.

Method of Making a Hydrogel

FIG. 9 shows a flow diagram of a method 900 including combining a gold salt with a cationic surfactant to form a salt-surfactant mixture (block 902), heating an agarose-water mixture to form a substantially clear solution (block 904), combining the salt-surfactant mixture with the substantially clear solution to form a hydrogel solution (block 906), introducing the hydrogel solution into a mold to form a shaped-hydrogel (block 908), and diffusing ascorbic acid into the shaped-hydrogel to form a substantially colorless shaped-hydrogel (block 910). In some embodiments, combining the gold salt with the cationic surfactant to form the salt-surfactant mixture includes mixing a solution of 50 mM C₁₆TAB with a solution of 10 mM AU³⁺. In some embodiments, combining the salt-surfactant mixture with the substantially clear solution to form a hydrogel solution includes combining substantially equal amounts of the salt-surfactant and the substantially clear solution. In some embodiments, introducing the hydrogel solution into the mold to form the shaped hydrogel includes providing a disc shape mold to receive the hydrogel solution. In some embodiments, the method 900 further includes radiating the substantially colorless hydrogel.

In some embodiments a nanosensor includes five components (1) Gold salt, (2) Cationic surfactant, (3) Ascorbic acid, (4) Agarose and (5) water. 600 μL of 50 mM C₁₆TAB is mixed with 30 μL of 10 mM Au3+. Agarose is dissolved in water to yield the required weight percentage. The agarose mixture is heated until a clear solution is obtained. 500 μL of the agarose is mixed with 500 μL of the gold-surfactant mixture. 650 μL of this liquid mixture is allowed to set in prefabricated molds which results in agarose discs with 1.5 cm in diameter. 650 μL of 10 mM ascorbic acid is allowed diffuse into the gel for 10 minutes leading to the formation of a transparent hydrogel. Addition of ascorbic acid to Au3+ reduces it from a trivalent state to a monovalent Au+ ion. Addition of cationic surfactant prevents complete conversion of Au3+ to gold nanoparticles. In the presence of ionizing radiation water split into three free radicals. Among these three radicals (1) hydrated electrons and (2) hydrogen are reducing in nature which assist in conversion of metal ions to their zerovalent forms reading it. These zerovalent metal nucleate and grow into metal nanoparticles which are capped by the cationic surfactant.

Apparatus

FIG. 10 shows a block diagram of an apparatus 1000 including a substantially colorless hydrogel 1002 to receive a low dose of radiation 1004 and form a radiated hydrogel 1006 having a color, and a detector 1008 optically coupled to the radiated hydrogel 1006. The detector 1008 is optically coupled to the radiated hydrogel 1006 by an optical path 1010. In some embodiments, the substantially colorless hydrogel 1002 includes a metallic salt. In some embodiments, the metallic salt includes a gold salt. In some embodiments, the detector 1008 includes a spectrophotometer 1012. In some embodiments, the detector 1008 includes a human visual system 1014. A human visual system is suitable for use in a variety of color measurement tasks and in particular for identifying changes in color. In some embodiments, the radiated hydrogel 1006 has a color and the color has a color intensity that increases with an increase in the low dose of ionizing radiation 1004.

The low dose of ionizing radiation 1004 is not limited to a particular radiation value. In some embodiments, the low dose of ionizing radiation 1004 includes a therapeutic range of values such as between about 0.5 Gy and about 2.0 Gy. In some embodiments, the low dose of ionizing radiation 1004 includes a range of values of between about 1.7 Gy and about 2.2 Gy. In some embodiments, the low dose of ionizing radiation 1004 includes a value of between about 3.0 Gy and about 10.0 Gy.

In operation, the substantially colorless hydrogel 1002 of the apparatus 1000 receives a low dose of ionizing radiation 1004 to form a radiated hydrogel 1006. In some embodiments, the radiated hydrogel 1006 includes a plasmonic nanoparticle 1016. A plasmonic nanoparticle is a particle whose electron density can couple with electromagnetic radiation having wavelengths that are larger than the particle due to the nature of the dielectric-metal interface between the medium and the particles.

The apparatus 1000 has sever advantages including providing spatial dose distribution, room temperature operation, use of visual spectrophotometer, and color change for visual identification of low dose ionizing radiation.

Experimental

Materials:

Gold(III) chloride trihydrate (HAuCl₄.3H₂O), trimethyloctylammonium bromide (C₈TAB) (≧98%), dodecyltrimethylammonium bromide (C₁₂TAB) (≧98%) and L-Ascorbic acid (AA) were purchased from Sigma-Aldrich. Cetyl trimethylammonium bromide (C₁₆TAB) was purchased from MP chemicals. All chemicals were used as received from the manufacturer without any additional purification.

Sample Preparation for Irradiation:

First, 30 μL of 0.01 M HAuCl₄ were mixed with 600 μL of 0.05 M C_x=8,12,16TAB. Upon addition of 30 μL (0.196 mM), 300 μL (1.96 mM), 600 μL (3.92 mM approximated as 4 mM) and 900 μL (5.88 mM) of 0.01 M L-Ascorbic acid, the solution turned colorless after shaking; the concentrations of ascorbic acid were thus varied in order to examine its effect on nanoparticle formation (FIGS. 12A-12B). Unless specifically mentioned, the volume of AA used is 900 μL. The measured pH of the solution was between 2.9 and 3.1. Samples were prepared at Banner-MD Anderson Cancer Center, Gilbert, Ariz. prior to radiation.

Radiation Conditions:

A TrueBeam linear accelerator was used to irradiate the samples. Samples were radiated at a dose rate of (15.6 Gy/min). The samples containing surfactant at a concentration of 20 mM and 10 mM were radiated at doses of 0 (Control), 1.1, 3.2, 5.3, 10.5, 15.8, 26.3, 36.9 and 47.4 Gy. These are reported as 0, 1, 3, 5, 10, 16, 26, 37 and 47 Gy respectively in the article. The samples containing surfactant at a concentration 2 mM and 4 mM were irradiated with 0 (Control), 0.5, 1, 1.5, 2, 2.5, 3, 5, 7.5, 10, 12.5 and 15 Gy. After irradiation the samples were transported back to Arizona State University in Tempe, Ariz. (one-way travel time of approximately 30 minutes).

Absorbance Spectroscopy: Absorbance profiles of the radiated and the control samples were measured using a BioTek Synergy 2 plate reader. Absorbance values from 150 μL of sample were measured from 300 to 900 nm with a step size of 10 nm in a 96 well plate. Nanopure water (18.2 MΩcm) was used as a blank in all cases. The absorbance was corrected for offset by subtracting A₉₀₀ nm and the presence of a peak between 500 and 700 nm was used as an indicator for gold nanoparticle formation.

Determination of Critical Micellar Concentration (CMC):

Pyrene (60 μL of 2×10⁻⁵M) in acetone was added to 20 ml glass vials. Upon acetone evaporation, 2 ml of C₁₆TAB of varying concentrations was added and stirred for 6 hours at room temperature. To achieve the similar conditions as the irradiation experiments, 30 μL of 10 mM gold salt+600 μL of the above prepared C₁₆TAB+900 μL of 10 mM ascorbic acid were mixed. A fluorescence spectrophotometer with an excitation scan range of 300-360 nm and an emission wavelength of 390 nm was used. Ratio of I₃₃₇/I₃₃₄ determined as a function of the surfactant concentration was used to calculate the CMC using pyrene as the probe based on methods described in the literature.

Dynamic Light Scattering (DLS) Measurements:

50 μL of the sample was transferred into a cuvette and placed into a Zetasizer Nano instrument. The software was set up to carry out measurements with autocorrelation. Thereafter, the average diameter along with the polydispersity index (PDI) were recorded based on the software readout.

Transmission Electron Microscopy (TEM):

Samples for TEM were prepared by casting a drop of the solution onto a carbon film on a copper mesh grid. The samples were then dried in air. The above process was repeated several times to ensure good coverage. Dried samples were visualized using a CM200-FEG instrument operating at 200 kV.

TABLE 1
Absorbance values measured 7 hours following exposure of
endorectal balloons with the plasmonic nanosensor (20 mM
C16TAB concentration) following exposure to different
doses of ionizing radiation. The calibration equation used was
Absorbance = 0.0092 * Dose − 0.0356. The 0 Gy data
point is outside the linear range (5-37 Gy) of the nanosensor, and
the nanosensor is able to detect X-ray radiation in the linear range.
		Calculated Dose	Average
Delivered	Measured	from the	Radiation Dose
Dose	Absorbance	calibration curve	Delivered ± S.D
(Gy)	(A.U)	(Gy)	(Gy)
0	0.003, 0.002, 0.009	4.19, 4.09, 4.85	4.38 ± 0.41
7.9	0.05, 0.015, 0.045	9.30, 5.50, 8.76	7.85 ± 2.05
10.5	0.061, 0.035, 0.032	10.50, 7.67, 7.35	8.51 ± 1.73

TABLE 2
X-ray Radiation dose determined using the plasmonic nanosensor
placed on an endorectal balloon in a prostate phantom as shown in
FIG. 8. The absorbance was determined 2 h after radiation exposure
using the equation Absorbance = 0.1597 * Dose − 0.0542. 0.5
Gy to 1.5 Gy was the dose range used for determining the calibration
curve. A C16TAB concentration of 2 mM was used in these studies.
Capsule No.		Calculated Dose	Average
(Actual Dose	Measured	from the	Radiation Dose
Delivered	Absorbance	calibration curve	Delivered ± S.D
in Gy)	(A.U)	(Gy)	(Gy)
1 (1)	0.12, 0.138, 0.154	1.09, 1.20, 1.30	1.20 ± 0.11
2 (1)	0.105, 0.154, 0.137	1.00, 1.30, 1.20	1.17 ± 0.16
3 (0.5)	0.016, 0.03, 0.025	0.44, 0.53, 0.50	0.49 ± 0.04

TABLE S1
Average hydrodynamic diameters of gold nanoparticles formed
after irradiation along with their corresponding polydispersity indices.
		Average		Average
		Diameter	STD DEV	Polydispersity
Surfactant	Dose	(nm)	Diameter (nm)	Index (PDI)
C16 20 mM	1 Gy	138.4	5.3	0.2
	3 Gy	122.8	1.9	0.2
	5 Gy	121.1	20.7	0.3
	10 Gy	102.3	13.2	0.2
	16 Gy	88.5	12.1	0.2
	26 Gy	72.6	4.7	0.2
	37 Gy	57.3	4.0	0.3
	47 Gy	45.5	3.4	0.3
C16 2 mM	0.5 Gy	81.9	8.9	0.3
	1 Gy	60.2	6.1	0.3
	1.5 Gy	48.2	7.3	0.4
	2 Gy	42.9	3.8	0.4
	2.5 Gy	39.8	3.6	0.4
C16 4 mM	1 Gy	133.4	10.4	0.2
	3 Gy	124.2	5.2	0.2
	5 Gy	105.3	6.3	0.2
	7.5 Gy	88.6	8.1	0.3
	10 Gy	92.6	8.6	0.3
	12.5 Gy	81.3	6.9	0.3
	15 Gy	74.2	5.5	0.3
	26 Gy	57.4	2.4	0.3
	37 Gy	32.0	0.4	0.5
	47 Gy	22.1	1.3	0.6
C16 10 mM	1 Gy	126.4	1.5	0.2
	3 Gy	127.1	1.6	0.2
	5 Gy	124.8	2.1	0.2
	10 Gy	124.9	5.0	0.2
	16 Gy	106.2	5.4	0.2
	26 Gy	72.2	7.1	0.2
	37 Gy	59.4	3.3	0.3
	47 Gy	50.9	2.3	0.2
C12 20 mM	1 Gy	141.6	32.2	0.5
	3 Gy	112.2	5.3	0.2
	5 Gy	75.2	5.0	0.3
	10 Gy	40.4	1.0	0.5
	16 Gy	23.9	1.1	0.6
	26 Gy	15.7	0.8	0.6
	37 Gy	17.9	0.7	0.6
	47 Gy	21.6	2.7	0.6

TABLE S2
A list of surfactants which could be potentially used as an alternative to the current surfactants.
Any derivative of the above compounds could also be potentially used.
		Molecular
Surfactant Name	Structure	Formula
Acetylcholine chloride ≥99% (TLC)		C7H16ClNO2
Aliquat ® 336
(2-Aminoethyl)trimethylammonium chloride hydrochloride 99%		C5H15ClN2 •HCl
Arquad ® 2HT-75
Benzalkonium chloride ≥95.0% (T)
Benzalkonium chloride
Benzalkonium chloride solution PharmaGrade.
Benzalkonium chloride solution ≥50% (via Cl), 50% in H20
Benzyldimethyldecylammonium chloride ≥97.0% (AT)		C19H34ClN
Benzyldimethyldodecylammonium chloride ≥99.0% (AT)		C21H38ClN
Benzyldimethylhexadecylammonium chloride ≥97.0% (dried material, AT)		C25H46ClN
Benzyldimethylhexylammonium chloride ≥96.0% (AT)		C15H26ClN
Benzyldimethyl(2-hydroxyethyl) ammonium chloride ≥97.0% (AT)		C11H18ClNO
Benzyldimethyloctylammonium chloride ≥96.0% (AT)		C17H30ClN
Benzyldimethyltetradecylammonium chloride anhydrous, ≥99.0% (AT)		C23H42ClN
Benzyldimethyltetradecylammonium chloride dihydrate 98%		C23H42ClN 2H2O
Benzyldodecyldimethylammonium bromide ≥99.0% (AT)		C21H38BrN
Benzyldodecyldimethylammonium bromide purum, ≥97.0% (AT)		C21H38BrN
Benzyltributylammonium bromide ≥99.0%		C19H34BrN
Benzyltributylammonium chloride ≥98%		C19H34ClN
Benzyltributylammonium iodide 97%		C19H34IN
Benzyltriethylammonium bromide 99%		C13H22BrN
Benzyltriethylammonium chloride 99%		C13H22ClN
Benzyltriethylammonium chloride monohydrate 97%		C13H22ClN H20
Benzyltrimethylammonium bromide 97%		C10H16BrN
Benzyltrimethylammonium chloride purum, ≥98.0% (AT)		C10H16ClN
Benzyltrimethylammonium chloride 97%		C10H16ClN
Benzyltrimethylammonium chloride solution technical, ~60% in H2O		C10H16ClN
Benzyltrimethylammonium dichloroiodate 97%		C10H16Cl2IN
Benzyltrimethylammonium tetrachloroiodate ≥98.0% (AT)		C10H16Cl4IN
Benzyltrimethylammonium tribromide purum, ≥97.0% (AT)		C10H16Br3N
Benzyltrimethylammonium tribromide 97%		C10H16Br3N
Bis(triphenylphosphoranylidene)ammonium chloride 97%		C36H30ClNP2
Boc-D-Lys(2-Cl-Z)-OH ≥98.0% (TLC)		C19H27ClN2O6
(2-Bromoethyl)trimethylammonium bromide 98%		C5H13Br2N
(5-Bromopentyl)trimethylammonium bromide 97%		C8H19Br2N
(3-Bromopropyl)trimethylammonium bromide 97%		C6H15Br2N
S-Butyrylthiocholine iodide puriss., ≥99.0% (AT)		C9H20INOS
Carbamoylcholine chloride 99%		C6H15ClN2O2
(3-Carboxypropyl)trimethylammonium chloride technical grade		C7H16ClNO2
Cetyltrimethylammonium chloride solution 25 wt. % in H2O		C19H42ClN
Cetyltrimethylammonium hydrogensulfate 99%		C19H43NO4S
(2-Chloroethyl)trimethylammonium chloride 98%		C5H13Cl2N
(3-Chloro-2-hydroxypropyl)trimethylammonium chloride solution purum, ~65% in H2O (T)		C6H15Cl2NO
(3-Chloro-2-hydroxypropyl)trimethylammonium chloride solution 60 wt. % in H2O		C6H15Cl2NO
Choline chloride ≥99%		C5H14ClNO
Decyltrimethylammonium bromide ≥98.0%(NT)		C13H30BrN
Diallyldimethylammonium chloride ≥97.0% (AT)		C8H16ClN
Diallyldimethylammonium chloride solution 65 wt. % in H2O		C8H16ClN
Didecyldimethylammonium bromide 98%		C22H48BrN
Didodecyldimethylammonium bromide 98%		C26H56BrN
Dihexadecyldimethylammonium bromide 97%		C34H72BrN
Dimethyldioctadecylammonium bromide ≥98.0% (AT)		C38H80BrN
Dimethyldioctadecylammonium chloride ≥97.0% (AT)		C38H80ClN
Dimethylditetradecylammonium bromide ≥97.0% (NT)		C30H64BrN
Dimethyloctadecyl[3-(trimethoxysilyl)propyl] ammonium chloride solution 42 wt. % in methanol		C26H58ClNO3Si
Dodecylethyldimethylammonium bromide ≥98.0% (AT)		C16H36BrN
Dodecyltrimethylammonium chloride ≥99.0% (AT)		C15H34ClN
Dodecyltrimethylammonium chloride purum, ≥98.0% (AT)		C15H34ClN
Domiphen bromide 97%		C22H40BrNO
Ethyltrimethylammonium iodide ≥99.0%		C5H14IN
Girard's reagent T 99%		C5H14ClN3O
Glycidyltrimethylammonium chloride technical, ≥90% (calc. based on dry substance, AT)		C6H14ClNO
Heptadecafluorooctanesulfonic acid tetraethylammonium salt purum, ≥98.0% (T)		C16H20F17NO3S
Heptadecafluorooctanesulfonic acid tetraethylammonium salt 98%		C16H20F17NO3S
Hexadecyl(2-hydroxyethyl)dimethylammonium dihydrogen phosphate solution ~30% in H2O		C20H46NO5P
Hexadecyltrimethylammonium bisulfate purum, ≥97.0% (T)		C19H43NO4S
Hexadecyltrimethylammonium bromide ≥96.0% (AT)		C19H42BrN
Hexadecyltrimethylammonium chloride ≥98.0% (NT)		C19H42ClN
Hexadecyltrimethylammonium chloride solution purum, ~25% in H2O		Cl9H42ClN
Hexamethonium bromide ≥95.0% (AT)		C12H30Br2N2
Hexyltrimethylammonium bromide ≥98.0% (AT)		C9H22BrN
Hyamine ® 1622 solution 4 mM in H2O
Malondialdehyde tetrabutylammonium salt ≥96.0% (NT)		C19H39NO2
Methyltrioctylammonium bromide 97%		C25H54BrN
Methyltrioctylammonium chloride ≥97.0% (AT)		C25H54ClN
Methyltrioctylammonium hydrogen sulfate ≥95.0% (T)		C25H55NO4S
Methyltrioctylammonium thiosalicylate ≥95% (C)		C32H59NO2S
Myristyltrimethylammonium bromide 98% (AT)		C17H38BrN
(4-Nitrobenzyl)trimethylammonium chloride 98%		C10H15ClN2O2
OXONE ® tetrabutylammonium salt technical, ~1.6% active oxygen basis
Tetrabutylammonium acetate for electrochemical analysis, ≥99.0%		C18H39NO2
Tetrabutylammonium acetate 97%		C18H39NO2
Tetrabutylammonium acetate technical, ≥90% (T)		C18H39NO2
Tetrabutylammonium acetate solution 1.0 M in H2O		C18H39NO2
Tetrabutylammonium benzoate for electrochemical analysis, ≥99.0%		C23H41NO2
Tetrabutylammonium bisulfate puriss., ≥99.0% (T)		C16H37NO4S
Tetrabutylammonium bisulfate purum, ≥97.0% (T)		C16H37NO4S
Tetrabutylammonium bisulfate solution ~55% in H2O		C16H37NO4S
Tetrabutylammonium bromide ACS reagent, ≥98.0%		C16H36BrN
Tetrabutylammonium bromide ReagentPlus ®, ≥99.0%		C16H36BrN
Tetrabutylammonium bromide solution 50 wt. % in H2O		C16H36BrN
Tetrabutylammonium chloride ≥97.0% (NT)		C16H36ClN
Tetrabutylammonium chloride hydrate 98%		C16H36ClN
Tetrabutylammonium cyanate technical		C17H36N2O
Tetrabutylammonium cyanide purum, ≥95.0% (AT)		C17H36N2
Tetrabutylammonium cyanide 95%		C17H36N2
Tetrabutylammonium cyanide technical, ≥80%		C17H36N2
Tetrabutylammonium difluorotriphenylsilicate 97%		C34H51F2NSi
Tetrabutylammonium difluorotriphenylstannate 97%		C34H51F2NSn
Tetrabutylammonium glutaconaldehyde enolate hydrate ≥97.0% (T)		C21H41NO2 •xH2O
Tetrabutylammonium heptadecafluorooctanesulfonate ≥95.0% (H-NMR)		C24H36F17NO3S
Tetrabutylammonium hexafluorophosphate for electrochemical analysis, ≥99.0%		C16H36F6NP
Tetrabutylammonium hexafluorophosphate purum, ≥98.0% (CHN)		C16H36F6NP
Tetrabutylammonium hexafluorophosphate 98%		C16H36F6NP
Tetrabutylammonium hydrogen difluoride solution technical, ~50% in methylene chloride (T)		C16H37F2N
Tetrabutylammonium hydrogen difluoride solution ~50% in acetonitrile		C16H37F2N
Tetrabutylammonium hydrogensulfate anhydrous, free-flowing, Redi-Dri ™, 97%		C16H37NO4S
Tetrabutylammonium hydrogensulfate 97%		C16H37NO4S
Tetrabutylammonium iodide for electrochemical analysis, ≥99.0%		C16H36IN
Tetrabutylammonium iodide ≥99.0% (AT)		C16H36IN
Tetrabutylammonium iodide reagent grade, 98%		C16H36IN
Tetrabutylammonium methanesulfonate ≥97.0% (T)		C17H39NO3S
Tetrabutylammonium methoxide solution 20% in methanol (NT)		C17H39NO
Tetrabutylammonium nitrate purum, ≥97.0% (NT)		C16H36N2O3
Tetrabutylammonium nitrate 97%		C16H36N2O3
Tetrabutylammonium nitrite ≥97.0% (NT)		C16H36N2O2
Tetrabutylammonium nonafluorobutanesulfonate ≥98.0%		C20H36F9NO3S
Tetrabutylammonium perchlorate for electrochemical analysis, ≥99.0%		C16H36ClNO4
Tetrabutylammonium perchlorate ≥98.0% (T)		C16H36ClNO4
Tetrabutylammonium phosphate monobasic puriss., ≥99.0% (T)		C16H38NO4P
Tetrabutylammonium phosphate monobasic solution 1.0 M in H2O		C16H38NO4P
Tetrabutylammonium phosphate monobasic solution puriss., ~1 M in H2O		C16H38NO4P
Tetrabutylammonium succinimide ≥97.0% (NT)		C20H40N2O2
Tetrabutylammonium sulfate solution 50 wt. % in H2O		C32H72N2O4S
Tetrabutylammonium tetrabutylborate 97%		C32H72BN
Tetrabutylammonium tetrafluoroborate for electrochemical analysis, ≥99.0%		C16H36BF4N
Tetrabutylammonium tetrafluoroborate puriss., ≥99.0% (T)		C16H36BF4N
Tetrabutylammonium tetrafluoroborate 99%		C16H36BF4N
Tetrabutylammonium tetraphenylborate for electrochemical analysis, ≥99.0%		C40H56BN
Tetrabutylammonium tetraphenylborate puriss., ≥99.0% (NT)		C40H56BN
Tetrabutylammonium tetraphenylborate 99%		C40H56BN
Tetrabutylammonium thiocyanate purum, ≥99.0% (AT)		C17H36N2S
Tetrabutylammonium thiocyanate 98%		C17H36N2S
Tetrabutylammonium p-toluenesulfonate purum, ≥99.00% (T)		C23H43NO3S
Tetrabutylammonium p-toluenesulfonate 99%		C23H43NO3S
Tetrabutylammonium tribromide purum, ≥98.0% (RT)		C16H36Br3N
Tetrabutylammonium tribromide 98%		C16H36Br3N
Tetrabutylammonium trifluoromethanesulfonate ≥99.0% (T)		C17H36F3NO3S
Tetrabutylammonium triiodide ≥97.0% (AT)		C16H36I3N
Tetradodecylammonium bromide ≥99.0% (AT)		C48H100BrN
Tetradodecylammonium chloride ≥97.0% (AT)		C48H100ClN
Tetraethylammonium acetate tetrahydrate 99%		C10H23NO2 •4H2O
Tetraethylammonium benzoate for electrochemical analysis, ≥99.0%		C15H25NO2
Tetraethylammonium bicarbonate ≥95.0% (T)		C9H21NO3
Tetraethylammonium bistrifluoromethanesulfonimidate for electronic purposes, ≥99.0%		C10H20F6N2O4S2
Tetraethylammonium bromide ReagentPlus ®, 99%		C8H20BrN
Tetraethylammonium bromide reagent grade, 98%		C8H20BrN
Tetraethylammonium chloride for electrochemical analysis, ≥99.0%		C8H20ClN
Tetraethylammonium chloride hydrate		C8H20ClN •xH2O
Tetraethylammonium chloride monohydrate ≥98.0%		C8H20ClN •H2O
Tetraethylammonium cyanate technical		C9H20N2O
Tetraethylammonium cyanide purum, ≥95% (AT)		C9H20N2
Tetraethylammonium cyanide 94%		C9H20N2
Tetraethylammonium hexafluorophosphate for electrochemical analysis, ≥99.0%		C8H20F6NP
Tetraethylammonium hexafluorophosphate 99%		C8H20F6NP
Tetraethylammonium hydrogen sulfate ≥99.0% (T)		C8H21NO4S
Tetraethylammonium hydrogen sulfate ≥98.0% (T)		C8H21NO4S
Tetraethylammonium iodide puriss., ≥98.5% (CHN)		C8H20IN
Tetraethylammonium iodide 98%		C8H20IN
Tetraethylammonium nitrate ≥98.0% (NT)		C8H20N2O3
Tetraethylammonium tetrafluoroborate for electrochemical analysis, ≥99.0%		C8H20BF4N
Tetraethylammonium tetrafluoroborate purum, ≥98.0% (T)		C8H20BF4N
Tetraethylammonium tetrafluoroborate 99%		C8H20BF4N
Tetraethylammonium p-toluenesulfonate 97%		C15H27NO3S
Tetraethylammonium trifluoromethanesulfonate ≥98.0% (T)		C9H20F3NO3S
Tetraheptylammonium bromide ≥99.0% (AT)		C28H60BrN
Tetraheptylammonium iodide ≥99.0% (AT)		C28H60IN
Tetrahexadecylammonium bromide purum, ≥98.0% (NT)		C64H132BrN
Tetrahexadecylammonium bromide 98%		C64H132BrN
Tetrahexylammonium benzoate solution ~75% in methanol		C31H57NO2
Tetrahexylammonium bromide 99%		C24H52BrN
Tetrahexylammonium chloride 96%		C24H52ClN
Tetrahexylammonium hexafluorophosphate ≥97.0% (gravimetric)		C24H52F6NP
Tetrahexylammonium hydrogensulfate 98%		C24H53NO4S
Tetrahexylammonium hydrogensulfate ≥98.0% (T)		C24H53NO4S
Tetrahexylammonium iodide ≥99.0% (AT)		C24H52IN
Tetrahexylammonium tetrafluoroborate ≥97.0%		C24H52BF4N
Tetrakis(decyl)ammonium bromide >99% (titration)		C40H84BrN
Tetrakis(decyl)ammonium bromide ≥99.0% (AT)		C40H84BrN
Tetramethylammonium acetate techriical grade, 90%		C6H15NO2
Tetramethylammonium benzoate electrochemical grade, ≥98.5% (NT)		C11H17NO2
Tetramethylammonium bis(trifluoromethanesulfonyl)imide 97%		C6H12F6N2O4S2
Tetramethylammoniumbisulfate hydrate ≥98.0%		C4H13NO4S •xH2O
(calc. on dry substance, T)
Tetramethylammonium bromide ACS reagent, ≥98.0%		C4H12BrN
Tetramethylammonium bromide 98%		C4H12BrN
Tetramethylammonium bromide for electrochemical analysis, ≥99.0%		C4H12BrN
Tetramethylammonium chloride for electrochemical analysis, ≥99.0%		C4H12ClN
Tetramethylammonium chloride purum, ≥98.0% (AT)		C4H12ClN
Tetramethylammonium chloride reagent grade, ≥98%		C4H12ClN
Tetramethylammonium chloride solution for molecular biology
Tetramethylammonium formate solution 30 wt. % in H2O, ≥99.99% trace metals basis		C5H13NO2
Tetramethylammonium hexafluorophosphate ≥98.0% (gravimetric)		C4H12 F6NP
Tetramethylammonium hydrogen sulfate		C4H13NO4S •H2O
monohydrate crystallized, ≥98.0%
Tetramethylammonium hydrogensulfate hydrate 98%		C4H13NO4S •xH2O
Tetramethylammonium iodide 99%		C4H12IN
Tetramethylammonium nitrate 96%	(CH3)4N(NO3)	C4H12N2O3
Tetramethylammonium silicate solution		C4H13NO5Si2
15-20 wt. % in H2O, ≥99.99% trace metals basis
Tetramethylammonium sulfate hydrate		C8H24N2O4S •xH2O
Tetramethylammonium tetrafluoroborate purum, ≥98.0% (T)		C4H12BF4N
Tetramethylammonium tetrafluoroborate 97%		C4H12BF4N
Tetramethylammonium tribromide purum, ≥98.0% (AT)		C4H12Br3N
Tetraoctadecylammonium bromide purum, ≥98.0% (NT)		C72H148BrN
Tetraoctadecylammonium bromide 98%		C72H148BrN
Tetraoctylammonium bromide purum, ≥98.0% (AT)		C32H68BrN
Tetraoctylammonium bromide 98%		C32H68BrN
Tetraoctylammonium chloride ≥97.0% (AT)		C32H68ClN
Tetrapentylammonium bromide ≥99%		C20H44NBr
Tetrapentylammonium chloride 99%		C20H44ClN
Tetrapropylammonium perchlorate ≥98.0% (T)		C12H28ClNO4
Tetrapropylammonium bromide for electrochemical analysis, ≥99.0%		C12H28BrN
Tetrapropylammonium bromide purum, ≥98.0% (AT)		C12H28BrN
Tetrapropylammonium bromide 98%		C12H28BrN
Tetrapropylammonium chloride 98%		C12H28ClN
Tetrapropylammonium iodide ≥98%		C12H28IN
Tetrapropylammonium tetrafluoroborate ≥98.0%		C12H28BF4N
Tributylammonium pyrophosphate
Tributylmethylammonium bromide ≥98.0%		C13H30BrN
Tributylmethylammonium chloride ≥98.0% (T)		C13H30ClN
Tributylmethylammonium chloride solution 75 wt. % in H2O		C13H30ClN
Tributylmethylammonium methyl sulfate ≥95%		C14H33NO4S
Tricaprylylmethylammonium chloride mixture of C8-C10 C8 is dominant
Tridodecylmethylammonium chloride purum, ≥97.0% (AT)		C37H78ClN
Tridodecylmethylammonium chloride 98%		C37H78ClN
Tridodecylmethylammonium iodide 97%		C37H78IN
Triethylhexylammonium bromide 99%		C12H28BrN
Triethylmethylammonium bromide ≥99.0%		C7H18BrN
Triethylmethylammonium chloride 97%		C7H18ClN
Trihexyltetradecylammonium bromide ≥97.0% (T)		C32H68BrN
Trimethyloctadecylammonium bromide purum, ≥97.0% (AT)		C21H46BrN
Trimethyloctadecylammonium bromide 98%		C21H46BrN
Trimethyloctylammonium bromide ≥98.0% (AT)		C11H26BrN
Trimethyloctylammonium chloride ≥97.0% (AT)		C11H26ClN
Trimethylphenylammonium bromide 98%		C9H14BrN
Trimethylphenylammonium chloride ≥98%		C9H14ClN
Trimethylphenylammonium tribromide 97%		C9H14Br3N
Trimethyl-tetradecylammonium chloride ≥98.0% (AT)		C17H38ClN
(Vinylbenzyl)trimethylammonium chloride 99%		C12H18ClN
N-(Allyloxycarbonyloxy)succinimide 96%		C8H9NO5
3-Benzyl-5-(2-hydroxyethyl)-4-methylthiazolium chloride purum, ≥99.0% (AT)		C13H16ClNOS
3-Benzyl-5-(2-hydroxyethyl)-4-methylthiazolium chloride 98%		C13H16ClNOS
1-Butyl-2,3-dimethylimidazolium chloride ≥97.0% (HPLC/AT)		C9H17ClN2
1-Butyl-2,3-dimethylimidazolium hexafluorophosphate		C9H17F6N2P
1-Butyl-2,3-dimethylimidazolium tetrafluoroborate ≥97.0%		C9H17BF4N2
1,3-Didecyl-2-methylimidazolium chloride 96%		C24H47ClN2
1, 1-Dimethyl-4-phenylpiperazinium iodide ≥99.0% (AT)		C12H19IN2
1-Ethyl-2,3-dimethylimidazolium ethyl sulfate BASF quality, ≥94.5% (HPLC)		C9H18N2O4S
3-Ethyl-5-(2 -hydroxyethyl)-4-methylthiazolium bromide ≥98%		C8H14BrNOS
Hexadecylpyridinium bromide		C21H38BrN
Hexadecylpyridinium bromide ≥97.0%		C21H38BrN
Hexadecylpyridinium chloride monohydrate BioXtra, 99.0-102.0%		C21H38ClN •H2O
5-(2-Hydroxyethyl)-3,4-dimethylthiazolium iodide 98%		C7H12INOS
1-Methylimidazolium hydrogen sulfate 95%		C4H6N2 •H2SO4
Methyl viologen dichloride hydrate 98%		C12H14Cl2N2 •xH20
1,2,3-Trimethylimidazolium methyl sulfate BASF quality, 95%		C7H14N2O4S
DL-α-Tocopherol methoxypolyethylene
glycol succinate
DL-α-Tocopherol methoxypolyethylene
glycol succinate solution 2 wt. % in H2O
DL-a-Tocopherol methoxypolyethylene
glycol succinate solution 5 wt. % in H2O
Aliquat ® HTA-1 High-Temperature Phase
Transfer Catalyst, 30-35% in H2O
Bis[tetrakis(hydroxymethyl)phosphonium] sulfate solution technical, 70-75% in H2O (T)		C8H24O12P2S
Dimethyldiphenylphosphonium iodide purum, ≥98.0% (AT)		C14H16IP
Dimethyldiphenylphosphonium iodide 98%		C14H16IP
Methyltriphenoxyphosphonium iodide 96%		C19H18IO3P
Methyltriphenoxyphosphonium iodide technical, ≥96.0% (AT)		C19H18IO3P
Tetrabutylphosphonium bromide 98%		C16H36BrP
Tetrabutylphosphonium chloride 96%		C16H36ClP
Tetrabutylphosphonium hexafluorophosphate for electrochemical analysis, ≥99.0%		C16H36F6P2
Tetrabutylphosphonium methanesulfonate ≥98.0% (NT)		C17H39O3PS
Tetrabutylphosphonium tetrafluoroborate for electrochemical analysis, ≥99.0%		C16H36BF4P
Tetrabutylphosphonium p-toluenesulfonate ≥95% (NT)		C23H43O3PS
Tetrakis(hydroxymethyl)phosphonium chloride solution 80% in H2O		C4H12ClO4P
Tetrakis(hydroxymethyl)phosphonium chloride solution technical, ~80% in H2O		C4H12ClO4P
Tetrakis[tris(dimethylamino) phosphoranylidenamino]phosphonium chloride ≥98.0%		C24H72ClN16P5
Tetramethylphosphonium bromide 98%		C4H12BrP
Tetramethylphosphonium chloride 98%		C4H14ClP
Tetraphenylphosphonium bromide 97%		C24H20BrP
Tetraphenylphosphonium chloride for the spectrophotometric det. of Bi, Co, ≥97.0%		C24H20ClP
Tetraphenylphosphonium chloride 98%		C24H20ClP
Tributylhexadecylphosphonium bromide 97%		C28H60BrP
Trihexyltetradecylphosphonium bis		C48H102O2P2
(2,4,4-trimethylpentyl)phosphinate ≥95.0%
Trihexyltetradecylphosphonium bromide ≥95%		C32H68BrP
Trihexyltetradecylphosphonium chloride ≥95.0% (NMR)		C32H68ClP
Trihexyltetradecylphosphonium dicyanamide ≥95%		C34H68N3P
ALKANOL ® 6112 surfactant
Adogen ® 464
Brij ® 52 main component: diethylene
glycol hexadecyl ether
Brij ® 52 average Mn ~330
Brij ® 93 average Mn ~357
Brij ® S2 main component: diethylene
glycol octadecyl ether
Brij ® S 100 average Mn ~4,670
Brij ® 58 average Mn ~1124
Brij ® C10 average Mn ~683
Brij ® L4 average Mn ~362
Brij ® O10 average Mn ~709
BRIJ ® O20 average Mn ~1,150
Brij ® S10 average Mn ~711
Brij ® S20
Ethylenediamine tetrakis(ethoxylate-block-
propoxylate) tetrol average Mn ~7,200
Ethylenediamine tetrakis(ethoxylate-block-
propoxylate) tetrol average Mn ~8,000
Ethylenediamine tetrakis(propoxylate-
block-ethoxylate) tetrol average Mn ~3,600
IGEPAL ® CA-520 average Mn ~427
IGEPAL ® CA-720 average Mn ~735
IGEPAL ® CO-520 average Mn 441
IGEPAL ® CO-630 average Mn 617
IGEPAL ® CO-720 average Mn ~749
IGEPAL ® CO-890 average Mn ~1,982
IGEPAL ® DM-970
MERPOL ® DA surfactant 60 wt. % in
water: isobutanol (ca. 50:50)
MERPOL ® HCS surfactant
MERPOL ® OJ surfactant
MERPOL ® SE surfactant
MERPOL ® SH surfactant
MERPOL ® A surfactant
Poly(ethylene glycol) sorbitan tetraoleate
Poly(ethylene glycol) sorbitol hexaoleate
Poly(ethylene glycol) (12) tridecyl ether
mixture of C11 to C14 iso-alkyl ethers with
C13 iso-alkyl predominating
Poly(ethylene glycol) (18) tridecyl ether
mixture of C11 to C14 iso-alkyl ethers with
C13 iso-alkyl predominating
Polyethylene-block-poly(ethylene glycol)
average Mn ~575
Polyethylene-block-poly(ethylene glycol)
average Mn ~875
Polyethylene-block-poly(ethylene glycol)
average Mn ~920
Polyethylene-block-poly(ethylene glycol)
average Mn ~1,400
Sorbitan monopalmitate
2,4,7,9-Tetramethyl-5-decyne-4,7-diol
ethoxylate average Mn 670
2,4,7,9-Tetramethyl-5-decyne-4,7-diol,
mixture of (±) and meso 98%
Triton ™ N-101, reduced
Triton ™ X-100
Triton ™ X-100 reduced
Triton ™ X-114, reduced, ≥99%
Triton ™ X-114, reduced
Triton ™ X-405, reduced
TWEEN ™ 20 average Mn ~1,228
TWEEN ™ 40 viscous liquid
TWEEN ™ 60 nonionic detergent
TWEEN ™ 85
indicates data missing or illegible when filed

Reference throughout this specification to “an embodiment,” “some embodiments,” or “one embodiment.” means that a particular feature, structure, material, or characteristic described in connection with the embodiment is included in at least one embodiment of the present disclosure. Thus, the appearances of the phrases such as “in some embodiments,” “in one embodiment,” or “in an embodiment,” in various places throughout this specification are not necessarily referring to the same embodiment of the present disclosure. Furthermore, the particular features, structures, materials, or characteristics may be combined in any suitable manner in one or more embodiments.

Although explanatory embodiments have been shown and described, it would be appreciated by those skilled in the art that the above embodiments cannot be construed to limit the present disclosure, and changes, alternatives, and modifications can be made in the embodiments without departing from spirit, principles and scope of the present disclosure.

Claims

1. A method comprising: combining a gold salt with a cationic surfactant to form a salt-surfactant mixture;heating an agarose-water mixture to form a substantially clear solution;combining the salt-surfactant mixture with the substantially clear solution to form a hydrogel solution;introducing the hydrogel solution into a mold to form a shaped-hydrogel; anddiffusing ascorbic acid into the shaped-hydrogel to form a substantially colorless shaped-hydrogel.

2. The method of claim 1, wherein combining the gold salt with the cationic surfactant to form the salt-surfactant mixture comprises mixing a solution of 50 mM C16TAB with a solution of 10 mM AU3+.

3. The method of claim 1, wherein combining the salt-surfactant mixture with the substantially clear solution to form a hydrogel solution comprises combining substantially equal amounts of the salt-surfactant and the substantially clear solution.

4. The method of claim 1, wherein introducing the hydrogel solution into the mold to form the shaped hydrogel comprises providing a disc shape mold to receive the hydrogel solution.

5. The method of claim 1, further comprising radiating the substantially colorless hydrogel.

6. A composition of matter comprising a hydrogel including a metallic salt, a cationic surfactant, ascorbic acid, agarose, and water.

7. The composition of claim 6, wherein the metallic salt comprises a gold salt.

8. The composition of claim 6, wherein the metallic salt comprises a salt of auric chloride (HAuCl4).

9. The composition of claim 6, wherein the cationic surfactant comprises cetyl trimethammoniom bromide (C16TAB).

10. The composition of claim 6, wherein the ascorbic acid comprises L-ascorbic acid.

11. An apparatus comprising: a substantially colorless hydrogel to receive a low dose of radiation and form a radiated hydrogel having a color; anda detector optically coupled to the radiated hydrogel.

12. The apparatus of claim 11, wherein the substantially colorless hydrogel comprises a metallic salt.

13. The apparatus of claim 12, wherein the metallic salt comprises a gold salt.

14. The apparatus of claim 11, wherein the detector comprises a spectrophotometer.

15. The apparatus of claim 11, wherein the detector comprises a human visual system.

16. The apparatus of claim 11, wherein the low dose of radiation has a value of between about 0.5 Gy and 2.0 Gy.

17. The apparatus of claim 11, wherein the low dose of radiation has a value of between about 1.7 Gy and about 2.2 Gy.

18. The apparatus of claim 11, wherein the low dose of radiation has a value of between about 3.0 Gy and about 10.0 Gy.

19. The apparatus of claim 11, wherein the radiated hydrogel has a color and the color has an intensity that increases with an increase in the low dose of radiation.

20. The apparatus of claim 11, wherein the radiated hydrogel comprises a plasmonic nanoparticle.

21. The method of claim 5, further comprising contacting the hydrogel with Na2S.

22. The method of claim 21, comprising contacting the hydrogel with a solution comprising Na2S.

23. The method of claim 21, wherein the Na2S diffuses into the hydrogel.

24. The method of claim 22, wherein the Na2S diffuses into the hydrogel.

25. The method of claim 23, wherein the Na2S diffuses into the hydrogel for about 5 minutes to about 15 minutes.

26. The method of claim 24, wherein the Na2S diffuses into the hydrogel for about 5 minutes to about 15 minutes.

27. The method of claim 21, wherein the contacting is for about 5 minutes to about 15 minutes.

28. The method of claim 22, wherein the contacting is for about 5 minutes to about 15 minutes.