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Review

Non-Invasive Nanoparticle Imaging Technologies for Cosmetic and Skin Care Products

by
Lynlee L. Lin
,
Kaitlin L. Nufer
,
Shoko Tomihara
and
Tarl W. Prow
*
Dermatology Research Centre, The University of Queensland, Translational Research Institute, 37 Kent Street, Woolloongabba, Brisbane, Queensland 4102, Australia
*
Author to whom correspondence should be addressed.
Cosmetics 2015, 2(3), 196-210; https://doi.org/10.3390/cosmetics2030196
Submission received: 26 May 2015 / Revised: 13 July 2015 / Accepted: 14 July 2015 / Published: 20 July 2015
(This article belongs to the Special Issue Nanotechnologies in Cosmetics)
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Versions Notes

Abstract

:
The nanotechnology field is growing at an unprecedented rate. This is resulting in significant benefits in skin care products and formulations. Likewise, imaging technology is also advancing. The convergence of these fields offers a unique opportunity to observe and quantify the interactions of nanoparticles within cosmetic and skin care formulations. More importantly, imaging technology holds tremendous promise for understanding how formulated nanoparticles interact with our skin. Imaging technologies can be broken into two major groups that include those that require invasive sample collection and processing (e.g., electron microscopy, mass spectrometry, and super-resolution structured illumination microscopy) and those that can be used in non-invasive data collection settings. Fluorescence microscopy, confocal microscopy, coherent anti-Stokes Raman scattering spectroscopy and optical coherence tomography fall into the latter category and are the focus of this review in the context of skin care product and cosmetics testing. Cosmetic and skin care product testing is most informative when carried out in volunteers. This makes invasive or disruptive analysis techniques unfeasible and supports the use of non-invasive imaging technologies. The combination of non-invasive imaging and minimally invasive microbiopsy sampling for combined imaging and molecular data is the future of skin care product testing.

1. Introduction

Breakthroughs in material science have led to nano-sized metal particles (<100 nm in diameter) to become increasingly available for sunscreen formulations. Nanoparticles are regularly included into skin care products and cosmetics for various reasons. For example, zinc oxide (ZnO) and titanium dioxides (TiO2) nanoparticles (NPs) are regularly incorporated into sunscreens as physical ultraviolet A (UVA) and ultraviolet B (UVB) blocking agents. ZnO and TiO2 at nanoscale level have improved transparency and aesthetic appearance on application [1]. More recently, poly(lactic-co-glycolic acid) (PLGA) nanoparticles as a transdermal delivery carrier were introduced for cosmetic applications [2,3]. As nanotechnology advances, more new nano-materials will be developed. It is imperative to characterise new materials and understand their interactions with complex biological systems such as skin.
The gold standard for nanoparticle imaging and characterisation is electron microscopy. Scanning electron microscopy (SEM) and transmission electron microscopy (TEM) are the two major classes of electron microscopy. SEM is commonly used to evaluate outcomes of cosmetics testing but the technique has also been frequently applied prior to commencing cosmetic studies to predict cosmetic biological interactions upon delivery. Morganti et al. [4] assessed Chitin Nanofibrril-Hyaluronan nanoparticles (CN-HA) for their ability to load an active anti-wrinkle agent and facilitate its penetration across the cutaneous barrier. Characterisation and size of CN-HA nanoparticles by SEM was used to establish the overall release rate of the active ingredient based on the entrapment of the active anti-aging ingredient and the efficacy and degradation profile of the polymer. Matos et al. also employed this technique to determine loading efficiency of minoxidil sulfate to Chitosan nanoparticles [5].
In addition to the characterisation of nanoparticles, SEM was employed to investigate the impact of common hair cosmetic products such as bleaches, dyes and shampoos and conditioners on hair properties [6]. SEM can provide morphological data like changes to hair morphology including breaking or lifting of cuticular scales and cuticle tearing and fragmentation. TEM, on the other hand, is the gold standard for visualising nanoparticles in tissues or cells and their size and distribution [7]. The location of TiO2-NP and ZnO-NP in sunscreen formulations were identified in vivo in porcine skin by Monteiro-Riviere et al. [8] using both TEM and SEM in UVB treated skin (Figure 1).
Despite the considerable advantages of electron microscopy, there are significant downfalls to this approach as summarised in Table 1. Sample preparation for imaging is a lengthy process and requires a high level of skill and training. Sample collection is invasive and often requires samples to be sectioned, restricting samples to single use only. This process makes real-time assessments and time point studies impractical. Electron microscopy is also prone to generating artefacts from residues from the sample preparation process as well as from nanoparticles themselves. This can make distinguishing nanoparticles from biological materials such as a cellular components or debris challenging [7]. Electron microscopy images also lack contrast in comparison to other non-invasive imaging techniques. Thus, although electron microscopy is a gold standard for materials science, it is not the most appropriate approach for answering questions about the interactions between skin care product formulations and volunteer skin. This review provides a survey of approaches that can be used in the investigation of nanoparticle-skin interactions in the context of cosmetics and skin care products.
Table
Table 1. Advantages and disadvantages of imaging techniques for nanoparticles associated with cosmetic and skin research.
Table 1. Advantages and disadvantages of imaging techniques for nanoparticles associated with cosmetic and skin research.
TechniqueAdvantagesDisadvantages
Scanning electron microscopy/Transmission electron microscopy
  • High resolution, visualization of individual nanoparticles.
  • Elemental analysis.
  • Sample preparation required.
  • Requires high level of skill and training.
  • Invasive procedure.
  • Lack of contrast.
Single photon laser scanning microscopy
  • Non-invasive procedure.
  • Real-time imaging.
  • Individual nanoparticles cannot be visualized due to low resolution.
  • Limited penetration depths of up to 200 µm in living tissue.
  • Requires labelling of samples.
Multiphoton microscopy
  • Non-invasive procedure.
  • Higher penetration depth of up to 500 µm in living tissue [9].
  • Real-time imaging.
  • Label-free.
  • Individual nanoparticles cannot be visualized due to low resolution.
  • Autofluorescence from tissue samples.
  • High cost.
  • Complexity of system.
Optical coherence tomography
  • Non-invasive procedure.
  • Real-time imaging.
  • Label free.
  • High penetration depth.
  • Individual nanoparticles cannot be visualized due to low resolution.
Coherent anti-Stokes Raman Scattering
  • Non-invasive procedure.
  • Real-time imaging.
  • Label-free.
  • Quantitative assessment.
  • Individual nanoparticles cannot be visualized due to low resolution.
  • High cost.
  • Complexity of system.
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Figure 1. Transmission election micrographs of various diluted TiO2-nanoparticles (NP) in ultrapure water and in porcine skin: (a) CM 630, 10% TiO2 (T-Lite SF); (b) CM 634, 10% TiO2 (T-Lite SF); (c) CM 643, 5% ZnO (Z-COTE HP1); (d) CM 644, 5% ZnO (Z-COTE). TEM images of stratum corneum are shown of (e) CM 630 treated, UVB-exposed skin; (f) high magnification of CM 634 treated, UVB-exposed skin; (g) CM 643 treated, UVB-exposed skin; (h) CM 644 treated, UVB-exposed skin. The black bars represent 100 nm. The white bars in (e, h), (f) and (g) are 4 µm, 1 µm and 250 nm, respectively. Reproduced with permission from [8], published by Oxford University Press, 2011.
Figure 1. Transmission election micrographs of various diluted TiO2-nanoparticles (NP) in ultrapure water and in porcine skin: (a) CM 630, 10% TiO2 (T-Lite SF); (b) CM 634, 10% TiO2 (T-Lite SF); (c) CM 643, 5% ZnO (Z-COTE HP1); (d) CM 644, 5% ZnO (Z-COTE). TEM images of stratum corneum are shown of (e) CM 630 treated, UVB-exposed skin; (f) high magnification of CM 634 treated, UVB-exposed skin; (g) CM 643 treated, UVB-exposed skin; (h) CM 644 treated, UVB-exposed skin. The black bars represent 100 nm. The white bars in (e, h), (f) and (g) are 4 µm, 1 µm and 250 nm, respectively. Reproduced with permission from [8], published by Oxford University Press, 2011.
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2. Non-Invasive Imaging Techniques

2.1. Single-Photon Confocal Microscopy

Single-photon confocal microscopy, more commonly known as laser scanning confocal microscopy (LSCM) is one of the most widely applied non-invasive, real-time imaging technique. LSCM is a fluorescence-based technique that captures high resolution images by focusing coherent light through a pinhole filter thus removing out of focus light from above or below the specimen before it reaches the detector [10]. The capacity for LSCM to optically section biological sample without compromising its structure provides an option for researchers to investigate and understand nanoparticle interactions with skin, characterise nanoparticle and biomolecule distribution, penetration and overall delivery pathway across the cutaneous barrier. However, the ability of the LSCM to visualise morphological structure of biological samples depends on the set-up of the microscope (i.e., type of laser and optics). The visualisation of cellular morphology of the samples typically requires the use of a laser within visible or near-infrared range.
Reflectance confocal microscopy (RCM) is a form of LSCM that uses the visible to near-infrared spectrum to provide en face optical sections of the skin at a quasi-histological resolution [11]. RCM has been used clinically for the differential diagnosis of basal cell carcinoma [12] and melanoma [13] in addition to a host of other dermatological conditions. We are the first group to assess the penetration profile of topical nanoparticles in human skin using RCM [14,15]. We observed that topically applied nanoparticles were resolved as highly reflective aggregates. In 2011, we investigated the penetration profile of gold (Au-NP) and silver (Ag-NP) nanoparticles in ex vivo [14] and in vivo [15] human skin models. One would assume that the potential for nanoparticle penetration would increase if the protective outer barrier of the skin, stratum corneum, is compromised. Tape-stripping protocols were carried out to mimic this type of damage. Both Au-NP and Ag-NP aggregated on the skin surface and within the furrows, and did not enter viable epidermis even when the outer skin barrier was disrupted [14,15]. Our secondary goal in the silver nanoparticle study was also to assess the natural rate of nanoparticle clearance after topical application. Visible aggregates were observed up to 10 days in discrete areas of damaged skin but not in intact skin (Figure 2) [15].
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Figure 2. In vivo, en face reflectance confocal sections of human skin applied with ZnO-NP. Silver nanoparticles, indicated by white arrowheads, were seen aggregating on the skin surface for up to 6 days (data not shown) in intact skin and up to 10 days in barrier-disrupted skin. The white bar represents 200 µm. Reproduced with permission from [15], published by Elsevier B.V., 2011.
Figure 2. In vivo, en face reflectance confocal sections of human skin applied with ZnO-NP. Silver nanoparticles, indicated by white arrowheads, were seen aggregating on the skin surface for up to 6 days (data not shown) in intact skin and up to 10 days in barrier-disrupted skin. The white bar represents 200 µm. Reproduced with permission from [15], published by Elsevier B.V., 2011.
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Tattoo inks and permanent make-up are also considered by the US Food and Drug Administration (FDA) as cosmetic products. Ink and pigments have been reported to contain carbon nanoparticles [16]. These products are usually administered through injection into the superficial dermis layer but they have not been approved by FDA for such application methods [17]. More than 150 adverse reactions to permanent make-up were reported to the FDA between 2003 and 2004. Maier et al. was the first group to use RCM for investigating the skin alteration in a 40-year-old female’s lip after undergoing a permanent lip lining procedure done at a cosmetic institute [18]. The patient reported substantial swelling, scaling and tenderness even after topical treatment with corticosteroid. Pigment as bright clusters of particles dispersed in the epidermis and superficial dermis using high-definition optical coherence tomography (HD-OCT) and RCM. Non-infectious granuloma that was made up of highly reflective structures with macrophages loaded with pigment was detected in both HD-OCT (Figure 3) and RCM images, and was further confirmed by a skin biopsy [18].
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Figure 3. High-definition optical coherence tomography image of lip treated with permanent make-up. Aggregated pigmentation and formation of granuloma-like structures (white arrow) was identified below the epidermis from a cross-sectional image (a). Scattered pigment consisting of bright structures with dark centre that corresponded to pigment loaded macrophage (white arrow) was observed from en face high-definition optical coherence tomography (HD-OCT) image (b). Reproduced with permission from [18], published by European Academy of Dermatology and Venereology, 2014.
Figure 3. High-definition optical coherence tomography image of lip treated with permanent make-up. Aggregated pigmentation and formation of granuloma-like structures (white arrow) was identified below the epidermis from a cross-sectional image (a). Scattered pigment consisting of bright structures with dark centre that corresponded to pigment loaded macrophage (white arrow) was observed from en face high-definition optical coherence tomography (HD-OCT) image (b). Reproduced with permission from [18], published by European Academy of Dermatology and Venereology, 2014.
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Particle size and dispersion are important performance factors for sunscreen products [19]. It is unknown if these properties changes when raw TiO2-NP are incorporated into sunscreen formulations. In order to accurately assess these changes, the characterisation methods employed have to be performed without the need to dilute or modify samples. Wokovich and his group employed three different techniques to determine the impact of formulation process to size or shape of TiO2-NP [20]. Four different sunscreen formulations were assessed in intact porcine skin: a sunscreen vehicle with no nanoparticles, uncoated 21 nm TiO2-NP, coated 50 nm TiO2-NP and a submicron sized 250 nm TiO2-NP. LCSM has a resolution limitation of 200 nm where identification and imaging of individual nanoparticles is not possible. This means that a single nanoparticle signal can theoretically be detected within a single pixel, but the device cannot distinguish whether the signal arises from one or more nanoparticles spatially. Wokovich et al. were able to evaluate nanoparticle dispersion and penetration depth through the skin. LSCM was used in conjunction with invasive methods of higher resolutions including X-ray diffraction (elemental analysis) and SEM, to analyse nanoparticle delivery and penetration to the skin. However, we have found that electron microscopy approaches like this are prone to processing contamination artefacts and low signal strength that make results interpretation difficult. LSCM of sunscreens containing uncoated TiO2-NP and submicron TiO2-NP saw an even distribution and was confirmed by SEM. Coated TiO2-NP sunscreen showed uneven particle distribution with SEM confirming particles to appear as aggregates on the skin surface [20].
In addition to the technique’s resolution limits, skin and its cellular components are often difficult to analyse using LSCM. Repeated imaging using laser light sources risks irradiation damage in living tissues, particularly for in vivo studies. The generation of autofluorescence while imaging is one of the most problematic obstacles when using LSCM. However, this can be avoided by using a dual channel setup to separate signals from the fluorophore and sample [19]. Laser confocal microscopes also come at a significant purchase and maintenance costs.

2.2. Multiphoton Microscopy and Time-Correlated Single-Photon Counting

Multiphoton microscopy (MPM), also known as multiphoton tomography (MPT) offers real-time in vivo imaging and has become a relevant tool for the investigation of nanoparticles in living cells and tissue given its high image resolution, contrast and capacity to make use of skin autofluorescence [21]. MPM utilises femtosecond pulsed lasers to excite endogenous and exogenous fluorophores including unlabelled nanoparticles [7]. MPM is often combined with additional detectors to distinguish signals between nanoparticles and endogenous fluorophores. Time correlated single photon counting (TCSPC) enables fluorescent lifetime imaging (FLIM). The pairing of TCSPC detectors results in a dye free assessment and the ability to quantitate data generated from simultaneous assessments [7].
Multiple studies have been carried out in human volunteers and human skin to determine if ZnO penetrates beyond the stratum corneum [22,23,24]. MPM is one of the techniques that were explored by our group to perform in vivo monitoring of ZnO-NP on both healthy and diseased skin. Two cohorts of volunteers were included in the study: subjects with no history of skin condition and those who had either psoriasis or atopic dermatitis. ZinClear-S 60 capric/caprylic triglyceride (CCT) nanoparticles, an active ingredient in sunscreens, was applied to the forearm of subjects in doses of 2 and 14 mg/cm2. Volunteers who had healthy, intact skin were subjected to tape-stripping and treated for 4 and 24 h, while those with diseased skin were treated for 2 h. Multiphoton-excited photoluminescence (MEP) signals from ZnO-NP was quantified simultaneously with nicotinamide adenine dinucleotide phosphate (NAD(P)H, a metabolic intracellular molecule) using multiphoton tomography coupled with TCSPC-FLIM.
MPM images showed ZnO-NP signal localised in the stratum corneum and in the furrows of intact and tape-stripped skin at 4 h. Higher levels of ZnO-NP signals were present in the stratum corneum of tape-stripped skin. The ZnO-NP signal was decreased to a minute level in tape-stripped skin after 24 h, suggesting that ZnO-NP was dissolved throughout the 24 h treatment period [23]. Strong ZnO-NP signal was detected in the thick stratum corneum layer at 2-h time point. This signal attenuated before the stratum granulosum and was absent in subsequent deeper layers. There was no detectable ZnO-NP signal in the superficial viable epidermis both in lesional and non-lesional ZnO-NP treated skin [23]. These data support the hypothesis that there is no penetration of ZnO-NP into viable human skin when topically applied.
This was further confirmed by another study where we showed that topical nanoparticle signal from sunscreens was removed by washing with soap and water followed by re-imaging (Figure 4) [25]. In our study the ZnO-NP were applied topically to the volar forearm of patients, 2 mg/cm2, massaged for 30 s and then exposed for a 2 h period and then imaged by MPT. Skin was washed with hospital grade soap for 10 s then re-imaged. The epidermis was analysed by 40 sections of 5.1­µm stepwise optical biopsy. ZnO-NP signal intensity was reported as a percentage. Intact skin resulted in a decrease of signal from 36% ± 17% to 2% ± 1% after the third wash. Tape-stripped skin resulted in 36% ± 19% ZnO-NP detection before washing, with a decrease to 3% ± 3% after the third wash. There was no significant difference in ZnO-NP signal prior to washing between the intact and tape-stripped skin [25]. Overall this study showed ZnO penetration evaluated using MPM and that these nanoparticles were able to be localized in the skin using MPT by semi-quantification of signal analysis. ZnO-NP did not penetrate into viable human skin unless the barrier was previously injured. This study also revealed that topical application of ZnO-NP can also be removed by washing the site.
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Figure 4. Multiphoton tomography of human skin applied with ZnO-NP. The rows are representative z-projection of the epidermal layers to superficial dermal-epidermal junction before wash, and after subsequent washes. CCT: Capric-caprylic triglyceride buffer. Reproduced with permission from [25], published by Future Medicine Ltd., 2013.
Figure 4. Multiphoton tomography of human skin applied with ZnO-NP. The rows are representative z-projection of the epidermal layers to superficial dermal-epidermal junction before wash, and after subsequent washes. CCT: Capric-caprylic triglyceride buffer. Reproduced with permission from [25], published by Future Medicine Ltd., 2013.
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These studies are highly advantageous to cosmetic development and consumer awareness. Due to high purchase, operation and maintenance costs and the requirement for extensive user training, in vivo nanoparticles interactions in human skin are not frequently assessed by multiphoton microscopy. This result was interesting because it showed how easily artefacts from large concentrations of nanoparticles can confound the interpretation of imaging data.

2.3. Optical Coherence Tomography

Optical coherence tomography (OCT) is a non-invasive technique that enables the internal cross-sectional imaging of the microstructural morphology of the skin in real-time. OCT is an emerging clinical imaging technology of inflammatory skin disease, skin cancers and wound healing. Now it is also expanding into the sphere of cosmetic dermatology and cosmetic testing. OCT imaging is done in vivo and captures 2-D or 3-D high resolution images, although these images have lower resolution than confocal techniques. Real-time qualitative and quantitative assessments can then be carried out in the process of cosmetic product testing. The non-invasive nature of this imaging technique also allows for treatment sites to be imaged repeatedly, and monitoring progressive changes in the skin following cosmetic application.
OCT imaging measures the echo time delay of reflected light through low coherence interferometry in the near-infrared wavelength [26]. During OCT imaging, low-coherence near-infrared light is targeted towards an identified site on the skin. Light is then backscattered from the internal microstructures. The magnitude and location of backscattered light from these structures generates a high resolution image [27].
Qualitative assessments of cosmetic products are often performed by OCT. Han et al. carried out a study employing OCT for the examination of the penetration and accumulation of four cosmetic creams to human hand skin and their impact on collagen synthesis levels. One cream contained soluble collagen, another claimed to stimulate collagen production. The remaining two tested creams contained no active ingredients. Swept source optical coherence tomography was performed in vivo in male adult volunteers across a time range from 5 to 120 min. Single intensity from OCT images in hand skin showed an increase in tissue depth in the epidermis only for the cream containing soluble collagen. Peaks were seen at 30 and 120 min [28]. From OCT images, it was also concluded that in the short term (5–15 min), the collagen soluble cream had no impact on tissue. This information was able to be used by researchers to provide consumers with timeframes to achieve best cosmetic outcomes.
Skin surface roughness and topography for a topical wrinkle reduction therapy was evaluated by Vasquez et al., again testing a topical cosmetic for stimulating collagen production. Changes to participant wrinkle profiles were assessed by calculating frequency distribution depths (FDD). FDD showed number of occurrences increasing in the microstructure region (0–50 µm) and decreasing in the fine structure region (50–170 µm) for areas that were treated with anti-aging product, with a 10% reduction in wrinkles. Depth distributions indicated a reduction in occurrence of wrinkles deeper than 170 µm [29].
Optical coherence tomography offers many advantages (Table 1) to cosmetic investigators, primarily due to the non-invasive nature of this technique which permits repeated imaging. OCT imaging allows quantitative and qualitative images to be collected and assessed in real time. Time point studies can be carried out with ease to detect changes in treated sites. Imaging of non-transparent tissues also becomes a possibility with OCT due to utilising longer wavelengths of light.

2.4. Advanced Raman Spectroscopy

Advanced label-free imaging technologies with exceptional sensitivity and high time resolution for emerging biomedical applications and medicine are reaching clinical research laboratories in recent years. Raman spectroscopy has been widely used as an analytical and diagnostic tool in various research fields including chemistry [30], physics, material science [31,32] and medicine [33,34] since 1930s. This technique has recently been explored extensively for biomedical applications [35] given its label-free optical imaging ability and the capacity to provide native chemical fingerprints of cells, tissues or biofluids based on inelastic scattering of a light. This inelastic scattering of a photon from a particular molecule is known as the Raman effect. The principle behind molecular chemical fingerprinting is based on the unique vibrational signature of a molecule associated with specific chemical structural bonds. Raman spectroscopy differs from other intrinsic imaging techniques as it is not limited by the number of endogenous fluorophores and is minimally affected by the local environment. A major limitation of this technique is the extremely weak scattering effect due to low photon conversion efficiency of 1:1018 resulting in long data acquisition time. Along with the need of high laser power usage and long integration times, the study of living biological specimens is severely limited.
Raman spectroscopy variants of enhanced sensitivity have been developed over the years to overcome current problems of spontaneous Raman scattering. Examples of improved vibrational signals along with video-rate imaging speed Raman spectroscopy is Coherent anti-Stokes Raman Scattering (CARS). A detailed review that covers the principle and set-up of CARS microscopy has been published by Evan and Xie in 2008 [36]. The scope of this review section is to discuss the use of advanced Raman spectroscopy technologies for sunscreen nanoparticles imaging.
Current imaging modalities must overcome existing constraints of localising metal nanoparticles within a structurally complex biological system such as skin to accurately assess their biological interactions. Most optical imaging techniques either lack adequate spatial resolution and/or depth penetration that are required to locate the particles at cellular level within intact tissues. One major limiting factor of existing label-free, non-invasive imaging techniques is the lack of capacity to segregate the metal nanoparticles from the biological specimen without the need of invasive pre-processing. This is with exception to ZnO-NP, which have intrinsic multi-photon fluorescence properties [23,37,38] as discussed in the earlier sections. CARS microscopy has received considerable attention over the last decade, particularly for biomedical applications. To date, there are no reported data on the use of this technique for assessing sunscreen associated nanoparticles in human volunteers. The use of CARS microscopy for ex vivo detection of ZnO-NP and TiO2-NP up till now was limited to fish models [39,40].
Moger et al. conducted an exploratory study using this non-invasive technique to locate metal oxide nanoparticles including ZnO-NP, cerium dioxide (CeO2) and TiO2-NP in gills of rainbow trout, Onchrhynchus mykiss [39]. They were targeting leaf-like structures, known as the lamella, within the gills of the fish. The structure of the lamella was first identified by comparing the CARS image to a histologically-stained section of the same region (Figure 5a,b). The contrast derived from CARS microscopy that correlated to the high stain uptake areas were carbon-hydrogen (CH) rich structures. Different sizes of the nanoparticles suspended in agarose can be seen from the CARS images, and they only observed larger particle aggregations when Forward-CARS (F-CARS) detection scheme was used. Smaller particles that were not present in the F-CARS images were explained either by the reduction in forward-detected signal due to particle-agarose interface or the signal falling below background level. Three-dimensional images of the fish gills that were exposed to 5000 µg/L TiO2 for either 24 h or 14 days were acquired to determine the location of nanoparticles aggregations within the tissue. They reported small aggregates of particles located in the periphery of lamella after two weeks of exposure (Figure 5c–e). Large clusters of particles of up to 100 µm in diameter were also reported to be seen inside the secondary lamella near the capillary after extended period of exposure with CARS microscopy.
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Figure 5. Coherent anti-Stokes Raman Scattering (CARS) image of gill lamella. Tomographic CARS image of 8 µm sections, acquired using Stokes and pump wavelengths of 924 nm and 125 nm, respectively (a). White light image of Schiff-stained section taken at 60× magnification (b), E: Epithelium; CVS: Central venous space; L: Lamella. Example of a trans-axial section of gill lamella that was exposed to TiO2 for two weeks (c). Panels (d) and (e) show cross-sectional image of vertical and horizontal dotted line, respectively [39]. The locations of nanoparticle clusters were highlight by the white arrows in panels (d) and (e).
Figure 5. Coherent anti-Stokes Raman Scattering (CARS) image of gill lamella. Tomographic CARS image of 8 µm sections, acquired using Stokes and pump wavelengths of 924 nm and 125 nm, respectively (a). White light image of Schiff-stained section taken at 60× magnification (b), E: Epithelium; CVS: Central venous space; L: Lamella. Example of a trans-axial section of gill lamella that was exposed to TiO2 for two weeks (c). Panels (d) and (e) show cross-sectional image of vertical and horizontal dotted line, respectively [39]. The locations of nanoparticle clusters were highlight by the white arrows in panels (d) and (e).
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The group conducted another extensive study in 2010 to investigate the of bioavailability well-characterised metal nanoparticles in zebra fish and rainbow trout [40]. Morphological characterisation of ZnO-NP, CeO2 and TiO2-NP was confirmed using TEM. Additionally, environmental scanning electron microscopy coupled with energy-dispersive X-ray analysis (ESEM-EDX) was used to determine the spectrum profiles of the nanoparticles in water and tissue samples. Formation of large aggregates was seen in water that was exposed to the nanoparticles on ESEM micrographs while EDX picked up traces of titanium in the samples. There is a high tendency of unmodified nanoparticles, in the absence of natural organic macromolecules, to flocculate into several micrometers in diameter aggregates and precipitate out of solution. This is supported by the lack of significant uptake of zinc in fish tissues. However, they could not confirm if this is lack of uptake is true or due to the masking by high level of Zn background in the tissues. They have also confirmed for the first time that TiO2-NP enters into the peripheral lamella of the gill through the water column after 14 days of exposure based on CARS analysis [40].

3. Conclusions

The gold standard for imaging nanoparticles is electron microscopy. This approach works for in vitro imaging but is not appropriate in the complex mixtures or biological environments that are relevant for cosmetics and skin care product testing. Single photon confocal microscopy has evolved into basic science and clinical spaces. Both are useful for examining nanoparticles employed in cosmetics and skin care products. Applications utilising single photon approaches are reliant on fluorescent dyes or the reflective nature of the nanoparticles of interest. The inherent strength of this approach is that it is non-invasive and has the potential to simultaneously collect morphological image data from reflectance imaging. Multiphoton microscopy is conceptually similar to single photon imaging but has some additional benefits and drawbacks. This approach can detect a number of metal nanoparticles with high resolution without the need for fluorescent dyes. Likewise there are a number of autofluorescent molecules in living cells that can be interrogated for information on the metabolic state of nanoparticle treated cells or tissue. It is clear that CARS imaging has great potential for signal separation and quantification in the context of nanoparticles in cosmetics and skin care products, but this has yet to be fully tapped. It seems that the field has significant promise for uptake of imaging technology. The field is also moving quickly in terms of molecular interactions between cosmetic/skin care product nanoparticles and skin responses in complex scenarios. Thus the future of cosmetic and skin care product testing is likely to evolve into more sophisticated imaging followed by minimally invasive skin sampling via microbiopsy for molecular correlation with the imaging outcomes [41,42,43,44]. Molecular imaging has the potential to add more substance to claim support and safety assurances.

Acknowledgments

We thank NHMRC APP1065802 and Epiderm Foundation for the financial support.

Author Contributions

Lynlee L. Lin contributed to Introduction, Section 2.4, and Conclusion, and edited the manuscript; Kaitlin L. Nufer contributed to Introduction, Section 2.2 and Section 2.3; Shoko Tomihara contributed to Section 2.1; Tarl W. Prow edited the manuscript.

Conflicts of Interest

The authors declare no conflict of interest.

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MDPI and ACS Style

Lin, L.L.; Nufer, K.L.; Tomihara, S.; Prow, T.W. Non-Invasive Nanoparticle Imaging Technologies for Cosmetic and Skin Care Products. Cosmetics 2015, 2, 196-210. https://doi.org/10.3390/cosmetics2030196

AMA Style

Lin LL, Nufer KL, Tomihara S, Prow TW. Non-Invasive Nanoparticle Imaging Technologies for Cosmetic and Skin Care Products. Cosmetics. 2015; 2(3):196-210. https://doi.org/10.3390/cosmetics2030196

Chicago/Turabian Style

Lin, Lynlee L., Kaitlin L. Nufer, Shoko Tomihara, and Tarl W. Prow. 2015. "Non-Invasive Nanoparticle Imaging Technologies for Cosmetic and Skin Care Products" Cosmetics 2, no. 3: 196-210. https://doi.org/10.3390/cosmetics2030196

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