Currently optical sensors for measuring considerable concentrations of specific components of solutions and their parameters attract persistent worldwide interest. One of the advantages of these sensors is that they permit one to determine simply concentrations both instrumentally and visually. These sensors include holographic sensors [1, 2] and photonic crystal sensors [3, 4]. They can be used for measuring the concentration of protons (pH) in water solutions, heavy metal ions [5-8], glucose in blood [7-12] and other biological liquids [13,14], bacterium spores [15,16], metabolites  bacterial growth [18,19], humidity and temperature responses [20,21].
Holographic sensors are quite promising because they are highly sensitive, are easy to operate, provide high enough accuracy and can be used for various applications. At present time they belong to sensors with a moderate sensitivity (10-5 -10 -1 mol•L-1), depending on the type of the analyzed component, the design and the composition of the sensor matrix. Such a sensitivity range is required, for example, in measurements of the glucose concentration in blood and other biological liquids. Holographic sensors represent a polymer hydrogel matrix grafted onto the surface of glass or transparent polymer films and doped with nanosize solid grains, so that their concentration changes periodically in space and the mean distance between the grains is much smaller than the visible-light wavelength.
Holographic diffraction gratings  are generated within photosensitive polymer-silver halide photographic emulsions upon exposure to a single collimated laser beam, which passes through the polymer film and then reflected back by a plane mirror. Interference between the mutually coherent incident and reflected beams generates a standing wave pattern which, after development and fixing, creates a three-dimensional pattern comprising fringes of ultrafine metallic silver grains embedded within the thickness (from 5 to 50
The main goal at this stage is the development of sensors for measuring the glucose concentration in blood - low-cost and simple to handle of test plates. In addition, we assume the possibility of the development of sensors to control the conditions of transport and storage of vaccines, serums, ferment preparations, food, and also simple test systems in homes. In our opinion, the study of mechanisms of changes in the holographic response will make it possible to perform the precise adjustment of a sensor for particular operating conditions.
2. Results and discussion
Photosensitized nanocrystals of AgBr were synthesized in the hydrogel matrix by diffusion method . By exposing photographic emulsions in water or acetic acid (1%) solution to radiation from a He-Ne (632.8 nm, 15 mW) laser in the counter propagating-beam scheme, we obtained silver nanograins [23-28] with the period of layers providing the location of reflected radiation peaks in the operating region of the spectrometer. A number of matrices of different compositions and designs were investigated. Hydrogel matrices were consisted of three-dimensional polymer of acrylamide (AA), N, N’-methylene-bis-acrylamide (bis) as crosslinking agent and other comonomers: N-ε-methacryloyl-lysin (Lys), 2-(dimethylamino)-ethylmethacrylate (DMA), acrylic acid (AC), N-acryloyl-2-glucosamine (GA), N-acryloyl-3-aminophenylboronic acid (AMPh). Matrices based on copolymers of acrylamide with ionogen comonomers are sensitive to the solution acidity and ionic strength, while matrices based on aminophenylboronic acid are sensitive to glucose.
Figure 1 shows the typical reflection spectrum of the sensitive layer of a sensor. The reflection spectrum for the ideal layer should be described by the function (sin x/x)2. In our case, the spectrum is well described by a Gaussian. This is explained apparently the imperfect arrangement of silver grain layers.
Note that metal silver grains are located in the hologram in a very complex environment containing molecules and ions of solution, elements of the hydrogel matrix. When the solution composition is changed, the composition of ions in solution and the structure of the matrix itself are redistributed. As a result, the sensor response, i.e. the mean wavelength of reflected radiation changes, and the radiation intensity also changes due to the change in the diffraction efficiency of the hologram.
One of the most important properties of holographic sensors is reversibility of the response when changing composition of the solution (Fig.2). Figure 2a shows the time dependence of the reflection line shape during the transfer of the sensor based on aminophenylboronic acid from the citrate buffer to distilled water and back. This change is reversible. The complex shape of the line is explained by the inhomogeneous distribution of the distance between silver layers over depth. One can see that the diffraction efficiency decreases during layer swelling. Figure 2b presents the time dependences of the reflection line wavelength for aminophenylboronic acid sensor after the replacement of the alkali solution in a cell by the acid solution and vice versa (transition processes). The wavelength was measured during swelling and transition to the stationary state. In this case, the swelling changes monotonically and approximately exponentially. Figure 3 shows the time dependence of the reflection wavelength in the transition process after the replacement of the citrate buffer by distilled water. The initial state of this sensor was not stationary. The time dependences of the reflection wavelength and intensity are nonmonotonic, their signs being opposite. The nonmonotonic behavior can be explained by the complicated character of variations ionic composition of solution in the emulsion. It can be assumed that at the initial moment there is rapid diffusion of hydrogen ions from the hydrogel matrix. Then the dissociation of aminophenylboronic acid take place and negative charge appear on polymer chains. This leads to an increase in the period of the holographic grating and is accompanied by an increase in the wavelength of reflected light. The larger anion citrate diffuses slowly, and the system is gradually coming to an equilibrium state, which is accompanied by compression of the hydrogel matrix and decreasing the wavelength of the reflected light. The observed change in intensity, appear to reflect the change in the microenvironment of silver particles. This effect requires additional studies.
Figure 4a shows the response of the sensor located in the NaOH solution titrated hydrochloric acid with (the solution acidity was measured with a usual pH-meter). During titration, the reflected radiation wavelength and diffraction efficiency change drastically at the point where the solution acidity drastically changes. In this case, the diffraction efficiency changed almost by an order of magnitude. This means that the change in the ionic composition is accompanied not only by the swelling of hydrogel matrix of the sensor but also by a strong change in the scattering properties of a holographic layer. This fact was unknown before our studies. Figure 4b presents the dependences from Fig. 4a reduced to the same scale by using the following algorithm. For some dependence
Figure 5 shows the responses of sensors with acrylic acid to metal ions in a broad concentration range from 10-7 to 10-1M. They can be divided into three groups: 1- Pb, Co+ ions; 2- other bivalent metal ions; 3- alkali metal ions. The sensor is most sensitive to Pb2+ and Co3+ ions (10-5 M). Among the bivalent metal ions (Mg, Sr, Mn, Pb), the presence of Pb2+ ions in the solution led to the most noticeable contraction of the hydrogel and changes (542 nm, 37% contraction). The reflection maximum was shifted down by 320 nm with respect to that of the distilled water. The sensor sensitivity to Mg2+, Sr2+and Mn2+ ions was two orders of magnitude lower. Note that, unlike other metal ions, the sensor's response to the alkali metal ions (Na+, K+) is changed - the first wavelength increases (swelling of hydrogel occurs) and then decreases (shrinkage).
The sensor with acrylic acid can be used for determining the presence of metal ions in water (Fig.6). Figure 6a presents the reflection spectra of the sensor located in different solutions. Stationary response for distilled water is λ=735 nm while response for tap water - λ=615.2 nm which we explain by the presence of metal ions in tap water. The maxima of the reflection lines in water after filtration by household filters are located at 676 nm (Barrier filter) and 711.7 nm (Aquafor filter). The response of sensor on tap water is closer to position for mineral water containing calcium salt at concentration 3.10-3 M (λ=585.4 nm) and to lead salt (5.10-3 M) in distilled water (λ=542 nm). Sensors can be used repeatedly after regeneration, by washing them, for example, in sodium citrate and then in distilled water. A sensor response rapidly passes to the IR region (λ=860 nm) and then slowly passes to the stationary state (735 nm). Figure 6b shows the typical kinetics of the response maximum.
Fig.7 shows the responses of sensors for matrices of two types (with AC or AMPh) for different concentrations of ethanol in water. Figure 7a presents the reflection lines of a sensor based on acrylic acid for different concentrations of ethanol in water, while Fig. 7b shows the dependences of the reflection line wavelength on the ethanol concentration for this sensor and a sensor based on aminophenylboronic acid. The wavelength of reflected light at zero EtOH concentration depends both on the properties of the sensor matrix and on the recording conditions of holograms and can be changed in a controllable way within some range. The concentration dependence in the ethanol solution differs from that upon titration because in this case the decrease in swelling is probably caused by simple dehydration of solution inside the matrix, without ionization.
The spectral region of the sensor’s response can be modified in various ways: changing the composition of the solution in the recording hologram (swelling of the hydrogel matrix to change), using a laser at a different wavelength (e.g., instead of the He-Ne laser - semiconductor lasers with an appropriate photosensitizer) or changing the composition of the hydrogel matrix. This can be performed by varying the matrix design and selecting proper co-monomers and their concentrations. Figure 8 shows the dependences of the reflection line wavelength on the solution acidity for matrices of different compositions. One can see that the properties of the sensor response can be controlled in a broad range. Differences in the response of these sensors at titration of HCl solution correspond to pKa of components in polymeric matrices, when the charge changes and matrices swelling (or shrinkage) take place. Thus, we have instruments to influence on wavelength maximal response of the holographic system with aminophenylboronic acid from 450 nm (Lys) to 720 nm (DMA) at pH 7.4 (pH of blood serum). The response of the sensor AA-AMPh-GA pointed to the fast swelling when the pH solution is approaching to pKa= 8.9 aminophenylboronic acid and following slowly shrinkage of the polymeric matrix, at pH more 9.2 – only the swelling. The optical response can be a consequence of a number of different processes: diffusion of H+ out the gel, complex formation between GA and AMPh groups, and structural rearrangements of the gel due to the increasing concentration of negative charges resulting in gel hydration and swelling.
It is known that boronic acid can reversibly interact with 1,2-diols or 1,3-diols in aqueous solution to form 5- or 6-membered ring cyclic esters [27-30], (Fig.9). The neutral trigonal form of boronic acid molecules transforms into the anionic tetrahedral form on binding a saccharide, upon which a proton is released. Ester formation by interaction of the corresponding arylboronate with a diol is known to occur very fast and reversibly in aqueous media. Five and six membered cyclic arylboronate esters are formed upon binding between arylboronic acids and cis-1,2- or 1,3-diols respectively. With d-glucose the boronic acid has a choice of binding either the 1,2- or 4,6-diols, but with d-glucosamine hydrochloride, binding with just the 4,6-diol is possible. The stability constant with d-glucose is higher than that observed with d -glucosamine hydrochloride. It may be assumed that this behavior agrees with binding GA with tetrahedron B--atoms of boronic acid that carry into effect of additional crosslinking.
The quantitation of glucose is among the most important analytical tasks. It has been estimated that about 40% of all blood tests are related to it. In addition, there are numerous other situations where glucose needs to be determined, for example in biotechnology, in the production and processing of various kinds of feed and food, in biochemistry in general, and other areas. The significance of glycemic control for the prevention of diabetes complications is well established . The market for glucose sensors probably is the biggest single one in the diagnostic field, being about 30 billion $ per year today. Given this size, it is not surprising that any real improvement in glucose sensing (in whole blood and elsewhere) represents a major step forward. Holographic glucose sensors represent a comparatively new development [9-12, 18, 26]. The advantage of the holographic method over other optical techniques is the long-term stability of the sensor and the ease with which the wavelength may be tuned to suit the application.
Sensors with aminophenylboronic acid were sensitive to glucose concentrations in the solution. The reflection (λmax) and the shift (λ0-λmax) were influenced on the additive to polymer net, the buffer solution and pH. The shift of λmax is changed from 10 to 200 nm when glucose concentration was increased (0-30 mM). By investigating the properties of sensors in detail, we optimized responses of sensors to glucose. Their concentration dependences are shown in Fig.10.
One can see that the sensor sensitivity changes from 4.3 to 32 nm/(mmol.L-1). Copolymer of acrylamide containing 6 mol.% glucosamine, 6 mol.% boronic acid, 0.1 mol.% bis shows the most sensitivity in glycine solution, pH 7.4. The response of sensor to glucose in blood serum is lower but allows to distinguish changes in 1 mM glucose concentration. A possible reason for reducing the sensitivity of sensors to glucose in the blood serum is a contraction of the matrix caused by ionic strength. According to Fig. 11 at pH = 7.4 for all sensors including the GA and AMPh with increasing content of sodium ions to 0.14 M in the solution, there is a significant contraction of the hydrogel (20%). Therefore swelling of the hydrogel due to the presence of glucose occurs in the already highly compressed hydrogel
Holographic sensors give an interesting object in study of light scattering by an ensemble of nanoparticles, since one can change the environment of the particles almost preserving their mutual location. In these systems (see Fig. 4) we found that when the concentration of alkali changes in the titration, at the same time a sharp change in pH occurs, as well as a sharp change in the position of maximum reflection and a sharp and significant (almost by an order of magnitude) change in the diffraction efficiency of the holographic sensor. This indicates a significant change of the optical characteristics of the holographic layer [28, 33]. These characteristics include diffraction effectivity (DE), transmission, spectral form of the reflection line (in particular, its width) and wavelength distribution over the hologram surface. The line shape reflects homogeneity of the layer period into depth of the hologram. Its study allows investigating the transition processes in emulsion under change of solution. The transmittance and the line width together allow one to determine the effective number of layers and the weak inhomogeneity of the period. The processes in the sensitive hologram layer when changing solution parameters are complicated due to changing the molecular and ion structure in the solution within the hydrogel, to re-constructing the gel matrix, to interaction of the light-scattering grains with the solution components and matrix elements. Hologram based on silver nanoparticle layers is a typical nanoplasmonics object which scatters light in a complicated environment of ions of different kinds, of water molecules and of polymer matrix elements. The emulsion matrix interacts with the tested compounds by changing the density of crosslink in the polymer mesh. This may change as the charge distribution in the matrix and the composition of ions and other components in the solution. All of these elements (matrix elements, ions, molecules of the solution), interacting with each other and with silver nanograins, can alter the dynamic characteristics of electronic subsystems that match the light field, which leads to a change in optical characteristics. The research of these characteristics would help to understand the processes inside the emulsion and in the vicinity of nanograins.
If the period of layers is constant in depth and the modulation is weak (transmittance of a layer at the resonant wavelength λ is close to unity), the spectral width
The mode of sensor operation is very important. A good resolution is obtained when all the sensitive layer work effectively. If the falling radiation cannot penetrate sufficiently deep, the effective thickness of the hologram decreases. It reduces the resolution. Typically, the sensor sensitive layer contains silver nanograins, which have a high refractive index and a high absorption coefficient in the visible region of the spectrum. This leads to the elimination of radiation from the plane wave of light illuminating the hologram, due to absorption and scattering. This also reduces the number of effectively operating layers and, consequently, leads to the broadening of the reflection spectral line and to the deterioration of accuracy. The increase of the amplitude of modulation of the refractive index, which is introduced to increase the diffraction efficiency of the hologram, leads to the same effect. On the other hand, a strong decrease of the modulation amplitude narrows the line to the limit, but decreases the diffraction efficiency and, consequently, the measurement accuracy. Obviously, the parameters can be optimized. Therefore one needs a rather accurate method of determining the parameters of the hologram.
One of the important reasons to study optical properties of holographic sensors is to provide the proper work regime of the sensor. That means that the holographic sensor should work in the whole working range of concentrations as a thin photonic crystal (the reflectance is weak).
The hologram functioning depends seriously upon the light scattering properties. In its turn, these depend on both the type (metal or dielectric) and properties of the scattering center, and on its environment (mixture and ion concentration of the solution and of the hydrogel). The light scattering is the Raleigh one and can essentially limit the working range from the short wavelength side. Another important issue is to check the quality of the holographic layer, in particular, its homogeneity. To this purpose, we developed a colorimetric method of determination of the wavelength with the digital camera [34-36]. On the other hand, one can check the emulsion homogeneity by the distribution of the light scattering parameters.
The computer model of propagation in a layered medium for one-dimensional case was developed. The case of bleached holograms, where absorption is neglected and the refractive index is not depending from wavelength is included. At the same time is neglected and light scattering. Generalization to the dispersion of the refractive index is not an issue. The model allows determining the amplitude of modulation of the refractive index and effective thickness of the holographic layer by fitting the spectrum of the transmission hologram in the presence of the dip near the resonant frequency.
To measure the homogeneity of response of sensor properties over its surface have been applied the colorimetric method with the help of common camera [34-36]. Spatial inhomogeneity can emerge due either to inhomogeneities of the object under consideration, or to those of the sensor properties. The sensor is a thick layer hologram with width of few tens of micrometers. Its reflection spectrum has the spectral width 5-20 nm. Because of it, one suffices to use response from two color channels.
Hence, the problem is reduced to the following. Assume there is a set of emitters on a plane. We are interested in obtaining the spectra of each emitter preferably simultaneously. It is not easy especially if the sources are closely packed and produce almost continuous radiating surface. The situation is simpler if radiation from each point is spectrally narrow. Then, the distribution of the average radiation wavelength over the surface can be found by the colorimetric method. At each surface point one should determine with the required resolution the magnitudes of three components of a colour vector, i.e., obtain a colour image of the surface under study. Presently, the solution of this problem by using digital devices has no principal difficulties. The aim of our work is to solve the problem by means of conventional digital cameras. Each pixel of the colour image presents a particular colour vector in the RGB system. In order to find the distribution of the average wavelength from the image it is necessary to know how the particular digital camera represents radiation of different wavelengths.
The colorimetric method [34, 35] suggested for finding this distribution is as follows. Radiation passes to at least two detecting channels differing in spectral sensitivity. If in a certain spectral range (call it the working range) the ratio of spectral sensitivities of at least two channels is monotonous then one can determine the average wavelength of narrowband radiation from the signal ratio in the channels (see Fig. 12). At the selective sensitivity of the
The case of a finite spectral width is not as simple as that of a
In the general case, the colorimetric measurements imply a projection of the surface under study to the detecting array through two (or, for expanding the range, a greater number) types of light filters, i.e., it is necessary to create a colorimetric device with a sufficient spatial resolution. A digital camera is just such a device.
In Fig.13a, the spectral sensitivities are shown for three types of human eye cones responsible for colour recognition . A digital camera also distinguishes colours but the spectral sensitivity of its sensors is distinct. For example, we will show below that in the spectral range 540 – 575 nm a digital camera does not discriminate different colour hues at all. In Fig.13b, the signals of red (R), green (G), and blue (B) sensors of Sony F717 digital camera are shown that were obtained from a digital photograph of the incandescent lamp spectrum. The spectrum was detected from a spectrograph with a diffraction grating (~ 800 lines mm–1). This and all the following results were obtained at the sensitivity ISO 100 and switched-off automatic white balance. If the emission spectrum under study fits one of the two marked working ranges then the digital camera is appropriate for measurements. Note that we studied about ten various cameras and have found that their sensor characteristics are qualitatively similar. Figure 14 shows how a continuous spectrum (colour hue) is represented by digital cameras of various brands. Nevertheless, we did not study the characteristics of particular cameras as we wanted to understand the situation as a whole. Only the basic working Sony F717 digital camera was thoroughly studied. The spectrum of the incandescent lamp with an added calibrating spectrum of the mercury lamp was photographed. The shots used for the comparison were not overexposed, i.e., the maximal signal amplitude in channels was not above 150 – 200 digital units (the maximal admissible signal is 255 digital units). The colour hue H was determined in a standard way as the polar angle in the cylindrical coordinate system of a three-dimensional colour space. Its value was from 0 to 360. For convenient work in red, green, and blue colour ranges we chose the reference point for the colour hue in the blue range (H = 0 at R = 0, G = 0, B = 255). In this case, the break of the colour hue (0 – 360) fits the blue range and introduces no additional difficulties in data processing. The purely red colour (R = 255, G = 0, B = 0) corresponds to H = 120 and purely green colour (R = 0, G = 255, B = 0) corresponds to H = 240. A more thorough analysis of various digital cameras is interesting but is beyond the framework of the present paper. Anyway, some general information may be obtained from Fig. 13. The principal conclusion important for our work is that all the digital cameras used have a defect of colour sensitivity in the green range.
Some modern cameras provide the possibility for extracting unprocessed data in the RAW format. Preliminary experiments show that the situation with the colour sensitivity in this case is better. The processor of the digital camera does not distort data but further investigations are necessary for using the RAW format. At the first stage, we limited our study to simplest (mass) formats (JPEG, BMP) by the following reasons. Creation of holographic sensors was assumed for mass consumer and our aim was to develop not only a simple method for checking the quality of sensors but for reading data from them also. The method should be available for mass users, i.e., should rely on simplest digital cameras, in which the RAW format is not presented now. In addition, the processing of the image of the holographic sensor surface should be maximum simple.
A particular procedure for camera spectral calibration was developed because the responses of the three sensor types of the detecting array intricately depend not only on the radiation wavelength but on the exposure as well. The camera to be calibrated takes shots of a continuous spectrum superimposed on the mercury lamp spectrum with various exposures. Then, this spectrum is used for calibrating each image with respect to the wavelength. The images calibrated in this way are then processed together. The result is information on the relationship between the wavelength and sensor responses. The range 570 – 605 nm is considered in which the red and green sensors are sensitive. The signal in the blue channel in this range is not above the noise level. On the basis of all the obtained dependences the characteristic surface is plotted for the camera under study, which gives the sought-for wavelength as a function of the colour hue and the average value of
Note that in the case of the mercury spectrum image and continuous spectrum of the incandescent lamp each pixel is illuminated by an almost monochromatic light source, because the fraction of the continuous spectrum per single pixel of the image is less than 1 nm. Having processed the image of spectrum (in Fig. 15a, the domain is shown fitting the working wavelength range) we obtain the map of the wavelength distribution over the image (Fig. 15b); only the image domains from the processing system working ranges are taken into account. Domains with too low values of
By the digital image of the mercury spectrum for the yellow doublet lines and for underlying continuous spectrum we determined the standard deviation of the recovered wavelength in the limits of a narrow window oriented along the central (with respect to the spectrum) part of the mercury line. The window width was 4 pixels, which was less than the line width. The window height was 350 pixels and covered almost all the image of the mercury line and the whole corresponding part of the continuous spectrum. For the mercury doublet lines the wavelengths of 577 nm (the standard deviation is 0.16) and 579 nm (the standard deviation is 0.19) were obtained.
The developed method was employed for studying holographic sensors. The results are shown in Figs 16, 17. The spectrum of radiation reflected from a holographic sensor is wider and the problem of possible inaccuracy in determining the wavelength requires particular investigations. One should keep in mind that in using holographic sensors it is important to know the shift of the wavelength under the action of solution surrounding the sensor rather than the absolute value of the wavelength itself. Data presented in Figs 16a and 17a refer to a transient process to the hologram initially reflecting in the red range. Data for this hologram in ending stationary state is presented in Figs.16b. and 17b. One can see that the spread of wavelengths is noticeably reduced as compared to the transient process, and is less than 2 nm over the whole sensor surface. The local spread also strongly reduced and was less than 1 nm. The map comprises approximately 500 000 points.
The hologram quality and uniformity of the processes occurring during swelling can be estimated from their noise characteristics. In Fig. 18, the standard deviation of the calculated wavelengths is shown versus the width of the averaging window. The standard deviation of wavelength from mean is:
Further development of the colorimetric method with the use of RAW-format can significantly increase the working range of wavelengths (440-620 nm), which can be seen from Fig. 19.
Thus, here is described the method for measuring the distribution of the average wavelength for narrow-band radiation over the source surface by means of a commercial digital camera. There are the following limitations in using the method (without RAW-format): the radiation spectrum should be narrow (the average wavelength is determined); measurements are performed in the spectral range in which at least two sensor types of detecting array are simultaneously sensitive (for the most of cameras studied these ranges are 470 – 540 nm and 570 – 600 nm). The accuracy of the determined wavelength is not worse than 1 nm. The method was tested on the yellow doublet of the mercury spectrum and on a continuous spectrum of the incandescent lamp covering the working interval 570 – 600 nm. By using this method the uniformity of holographic sensor swelling was studied both in a stationary state and in dynamics.
The design of holographic sensors allows their use in multi-channel mode, when one sensor can simultaneously analyze multiple samples of the same type or define a few parameters of a sample. The holographic sensor is actually a thick hologram plane mirror about the size of a square centimeter. By placing such plate in a special cuvette, containing 24 cells of 2 mm diameter, each contains 50 μL of fluid to be analyzed; it can be used in a multi-channel mode for the simultaneous determination of all samples. The response of the sensor - the wavelength of reflected light - from the cell is easily determined by means of small-sized fiber-optic spectrometer (Fig. 20, 21) or in combination with the developed colorimetric method; it can greatly simplify and speed up the analysis (Fig. 19). As can be seen from Fig. 20, the wavelength of the reflected light at different points on the surface is almost the same (the standard deviation is 1.7 nm). This way you can see the spatial pattern of
kinetics of the holographic sensor, to conduct research of the spatial distribution of processes, with the help of special devices to conduct simultaneous analysis of different components or different samples. Fig. 21 presents the results of the determination of glucose in the blood serum of diabetic patients with glucose sensor (see Fig.) based on aminophenylboronic acid. Despite a significant decrease in the sensitivity of the sensor to the glucose concentration in blood plasma, determined by glucose clearly distinguished spectrometrically.
Thus, we have developed a colorimetric method of determination of the wavelength with the digital camera to study processes in inhomogeneous systems and to check the quality of the holographic layer. On this basis we revealed the multichannel simultaneous methods of analysis of spatially inhomogeneous objects and processes. We have found that the change in the ionic composition of solution is accompanied by the change in the distance between silver nanograin layers and in the diffraction efficiency of holograms. Based on this, we are formulated conditions for optimization of the operating mode of the holographic layer. Transition processes revealed variations in the reflection line shape, caused by the inhomogeneity of the sensitive layer, and non-monotonic changes in the emulsion thickness and diffraction efficiency. In this relation it was developed the computer model of propagation in a layered medium for one-dimensional case 33.
We have developed the method for manufacturing holographic sensors of different types and selected the composition of components of the hydrogel medium for the systems that can be used as bases for glucose sensors. The maximum mean holographic response in the mmol.L-1 region concentrations of glucose (1-20 mmol.L-1) per 1 mmol.L-1 of glucose in model solutions achieves ~40 nm/( mmol.L-1). It has been shown that holographic sensors can be used to determine the quality of water, in particular, for drinking, the acidity of media, ethanol concentration, ionic strength, metal ions and glucose in blood serum.
This work was supported by grant of the Program of Fundamental Studies “Fundamental Sciences for Medicine” of the Presidium of RAS.
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