Nanotheranostics 2022; 6(1):50-61. doi:10.7150/ntno.63222 This issue Cite


Review on Optical Imaging Techniques for Multispectral Analysis of Nanomaterials

Haeni Lee1,*, Jaeheung Kim1,*, Hyung-Hoi Kim2, Corresponding address, Chang-Seok Kim1, Corresponding address, Jeesu Kim1, Corresponding address

1. Department of Cogno-Mechatronics Engineering, College of Nanoscience & Nanotechnology, Pusan National University, Busan 46241, Republic of Korea.
2. Department of Laboratory Medicine and Biomedical Research Institute, Pusan National University Hospital and Pusan National University School of Medicine, Busan 49241, Republic of Korea.
*These authors contributed equally to this work.

Lee H, Kim J, Kim HH, Kim CS, Kim J. Review on Optical Imaging Techniques for Multispectral Analysis of Nanomaterials. Nanotheranostics 2022; 6(1):50-61. doi:10.7150/ntno.63222.
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Graphic abstract

Biomedical imaging is an essential tool for investigating biological responses in vivo. Among the several imaging techniques, optical imaging systems with multispectral analysis of nanoparticles have been widely investigated due to their ability to distinguish the substances in biological tissues in vivo. This review article focus on multispectral optical imaging techniques that can provide molecular functional information. We summarize the basic principle of the spectral unmixing technique that enables the delineation of optical chromophores. Then, we explore the principle, typical system configuration, and biomedical applications of the representative optical imaging techniques, which are fluorescence imaging, two-photon microscopy, and photoacoustic imaging. The results in the recent studies show the great potential of the multispectral analysis techniques for monitoring responses of biological systems in vivo.

Keywords: Multispectral imaging, Nanoparticles, Spectral unmixing, Contrast-enhanced imaging, Biomedical imaging


Biomedical imaging is an efficient way to investigate the physiological and morphological responses of biological cells, tissues, or organs. Especially, preclinical small animal studies have widely been conducted by visualizing the molecular responses, structural deformation, or material distribution in vivo [1]. Several biomedical imaging techniques such as X-ray computed tomography (CT) [2-4], magnetic resonance imaging (MRI) [5, 6], positron emission tomography (PET) [5, 6], single-photon emission computed tomography (SPECT) [7, 8], ultrasound imaging (USI) [9-11], and optical imaging [12] have been used for preclinical small animal studies. Among the biomedical imaging modalities, optical imaging techniques have been widely used due to their strong optical contrast without the use of ionizing radiation, which can potentially damage biological tissues. Compared to other imaging modalities, optical imaging techniques have several advantages, such as cost-effectiveness, real-time imaging capability, and ease of implementation. The basic principle of optical imaging is image formation according to the absorption or scattering of photons. In typical optical microscopes, the absorbed or scattered light beams form shadows in the resulting images, thus the transparency of the target specimen is visualized in resulting images. However, in biomedical optical imaging techniques such as fluorescence imaging (FLI) and two-photon microscopy (TPM), the relaxation of the absorbed light energy generates optical waves that are detected by optical sensors resulting in bright pixel values [13].

One major advantage of optical imaging is the ability to investigate molecular functional information from the multispectral imaging technique, which is the spectroscopy method acquiring both spatial (Nanotheranostics inline graphic and Nanotheranostics inline graphic axes) and spectral (Nanotheranostics inline graphic axis) information of biological tissue (Fig. 1). Image stacks are acquired by storing data under the illumination of various wavelengths of light to analyze the multispectral response. By comparing the pixel values at the same spatial position as a function of wavelength, we can delineate tissues with different spectral responses. Moreover, the composition of chromophores can be spectrally unmixed by mathematical calculation. The typical method to calculate the concentration of each chromophore is linear unmixing, which can be derived from the relationship that the measured signal is the weighted sum of the optical absorption coefficient of chromophores.

Nanotheranostics inline graphic  (1) 

where Nanotheranostics inline graphic is the measured optical signal in the Nanotheranostics inline graphic-th pixel at the Nanotheranostics inline graphic-th wavelength, Nanotheranostics inline graphic is the concentration of the Nanotheranostics inline graphic-th chromophore in the Nanotheranostics inline graphic-th pixel, Nanotheranostics inline graphic is the optical absorption coefficient of the Nanotheranostics inline graphic-th chromophore at the Nanotheranostics inline graphic-th wavelength, and Nanotheranostics inline graphic is the number of chromophores. The extended equation for all the pixels can be expressed as follows.

 Figure 1 

Schematic illustration of the spectral unmixing concept for the multispectral images. The images are reproduced with permission from Ref. [43]

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Nanotheranostics inline graphic  (2) 

where Nanotheranostics inline graphic is the number of wavelengths and Nanotheranostics inline graphic is the number of pixels in the image. Equation 2 can be simplified to the multiplication of matrices as follows, then the concentration of each chromophore in each pixel can be calculated through the pseudo-inverse operation. Note that the Nanotheranostics inline graphic and Nanotheranostics inline graphic are measured values and Nanotheranostics inline graphic is the unknown parameter that we have the interest to calculate.

Nanotheranostics inline graphic  (3) 
Nanotheranostics inline graphic  (4) 

In addition to the linear unmixing, the model-based technique has also been investigated for spectral unmixing [14]. In this technique, a model of spectral response is designed, then the amount of each component is calculated based on the model. Recently, deep learning technology has also been applied for the unmixing of the multispectral signal [15]. By using those methods, individual signals of each chromophore can be extracted from the composite of multispectral responses.

Because the optical absorption and scattering characteristics are the composition of the components in biological molecules, the biological or pathological changes can be revealed and monitored using multispectral imaging and analysis [16-18]. Therefore, the multispectral imaging techniques have widely applied and extended to biomedical studies for understanding the physiological response of biological tissues. In addition to the intrinsic chromophores, exogenous nanoparticles that generate optical contrast have widely been investigated for monitoring drug delivery, visualizing the biodistribution, and assessment of the therapy efficacy [19-21]. Since the optical absorption spectra of the nanoparticles are typically measured before the injection, the multispectral analysis with spectral unmixing also can be performed. Although optical imaging techniques have advantages of multispectral analysis, the major drawback that limits themselves in clinical applications is shallow penetration depth. The strong light scattering in biological tissue makes it difficult to maintain the optical focus beyond the optical transport mean free path (i.e., ~1 mm). Therefore, optical imaging techniques are typically used in preclinical small animal studies [22-24].

To overcome the shallow imaging depth of optical imaging methods, photoacoustic imaging (PAI) has widely been investigated. The unique difference of PAI from other optical imaging techniques is that the signal is delivered as acoustic waves, which are scattered much less in biological tissue. To capture the acoustic waves, ultrasound (US) transducers are typically used in PAI [25]. Compared to pure optical imaging, PAI can provide a deeper imaging depth of ~2-3 cm in soft tissue, while preserving the capability of multispectral analysis. Similar to the optical imaging techniques, multiple wavelengths of the excitation beams are used for multispectral analysis in PAI. Due to its relatively deep imaging depth, PAI has been applied to clinical studies [26-29] of breast cancers [30-32], thyroid cancers [33-36], prostate cancer [37], and melanoma [38, 39], as well as small animal studies [40-43].

Here, we review the multispectral imaging results of nanoparticles such that assessing molecular functional responses of biological systems in vivo. The principles of the typical multispectral imaging techniques (i.e., FLI, TPM, and PAI), which have been widely used for biomedical studies using nanomaterials, are summarized. By exploring the typical configurations, performance benchmarks, and representative biomedical applications of each technique, we highlight the advantages and limitations of multispectral imaging modalities. From the summary of the recent research articles which conducted multispectral analyses of nanomaterials in vivo, this article can provide future direction for biomedical imaging techniques to expand their application area.

Principles and Implementation of Imaging Systems

The typical multispectral imaging techniques for nanomaterials (i.e., FLI, TPM, and PAI) share a similar principle of the imaging mechanism, which is absorption and emission of energy (Fig. 2A) [44-46]. The energy is delivered in the form of light, illuminating the substance to be visualized. When the molecules in the ground state (S0 in Fig. 2A) absorb the photon energy, the electron in the outer shell is excited to the higher orbit, changes the state of molecules the excitation state energy level (S1 in Fig. 2A). The excited molecules return to the ground state again with a very short half-life time of typically a few nanoseconds. During this short period, the excited electron losses some amount of energy through vibration relaxation, generally dissipated as heat, then move to the lower state energy level (S2 in Fig. 2A). Consequently, the electron rapidly returns to the ground state by releasing its energy in the form of light (i.e., fluorescent light) or heat. Note that the wavelength of the emitted fluorescent (FL) light is longer than the wavelength of the excitation light. The wavelength of light can be expressed as the following equation.

Nanotheranostics inline graphic  (5) 

where Nanotheranostics inline graphic [m] is the wavelength of the light, Nanotheranostics inline graphic [Js] is Planck's constant, Nanotheranostics inline graphic [m/s] is the speed of the light, and Nanotheranostics inline graphic [J] is the quantum energy of the light.

FLI systems measure the intensity of the FL light emitted from the chromophores in biological tissue typically using charge-coupled device (CCD) cameras (Fig. 2B). To improve the contrast of the FL signal against the background signal, the fluorescence systems are generally designed so that the excitation and emitted lights pass through optical wavelength filters [47]. The excitation filter that filters the wavelength of the excitation light is selected as close to the peak absorption wavelength of the chromophore. The emission filter refines the emitted FL light, such that only desired wavelengths are passed to the CCD camera. To prevent the excitation light from being detected, a dichroic mirror with an appropriate transition wavelength is used in the integrated FLI system.

TPM is based on the selective non-linear excitation of the chromophores in a particular focal region [48]. Unlike FLI where a single photon is absorbed, two photons with half the energy (i.e., double the wavelength) from pulsed laser beams are used to excite the electron in TPM (two-photon excitation in Fig. 2A). The excitation of the molecules by the two photons is maximized at the focal region of the illuminated light (Fig. 2C). The FL light is emitted only at the focal region because the two-photon excitation is not high enough out of the focal region. Therefore, TPM can achieve 3D images by scanning the focal spot of the excitation light in Nanotheranostics inline graphic, Nanotheranostics inline graphic, and Nanotheranostics inline graphic directions.

In contrast to FLI and TPM, PAI uses heat release for the image contrast instead of FL light (Fig. 2D) [49]. The released heat makes the target molecules expand through thermoelastic expansion. Since PAI systems use short-pulsed laser beams, the heat is rapidly dissipated, and the expanded molecules shrink back to their original size. This rapid change creates thermoelastic expansion, then generates acoustic waves called photoacoustic (PA) waves [50]. The generated PA waves propagate in all directions and can be detected by the conventional US transducers (Fig. 2C). The unique feature of PAI is the acoustic detection of optical absorption properties of target specimens. In addition to the less scattering of the acoustic wave, which enables PAI to be used in deep tissue imaging [51, 52], the relatively slower propagation speed (1540 m/s in soft tissue) leads to the depth-resolved signal detection and thus 3D imaging is capable without scanning in the Nanotheranostics inline graphic direction.

The main difference between FLI/TPM and PAI is the form of energy release: irradiation of FL light or acoustic wave generation through thermoelastic vibration. However, the two types of energy release are mixed rather than either. The efficiency that an excited electron will emit the FL light can be express as follow.

Nanotheranostics inline graphic  (6) 

where Nanotheranostics inline graphic is the fluorescence quantum yield, Nanotheranostics inline graphic is the rate constant for radiative relaxation (i.e., rate of FL light emission), Nanotheranostics inline graphic is the rate constant for non-radiative relaxation (i.e., rate of heat release). In general, exogenous nanoparticles that are used as the contrast agents for these imaging techniques do not have 100% or 0% efficiency. In other words, both PAI and FLI/TPM can be performed [53-57] by injecting a single contrast-enhancing nanoparticle that has appropriate Nanotheranostics inline graphic (Table 1) [58].

 Figure 2 

Principles and implementation of typical multispectral imaging techniques. (A) Schematic diagram of principles of signal generation. Red arrows depict the excitation of an electron by absorbing light energy, and blue arrows depict the release of the absorbed energy. (B-D) Schematic illustrations of typical FLI, TPM, and PAI systems. Inset in (C) depicts TPE at the focal point of the excitation laser. FLI, fluorescence imaging; TPM, two-photon microscopy; PAI, photoacoustic imaging; TPE, two-photon excitation; EXF, excitation filter; EMF, emission filter; OL, optical lens; DM, dichroic mirror; OB, target object; CCD, charge-coupled device; OAC, optoacoustic combiner; PA photoacoustic; and DAQ, data acquisition module.

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 Table 1 

Optical characteristics of fluorophores that have been used for multimodal PAI and FLI/TPM. PAI, photoacoustic imaging; FLI, fluorescence imaging; TPM, two-photon microscopy; Nanotheranostics inline graphic, fluorescence quantum yield; PBS, phosphate-buffered saline; ICG, indocyanine green. The data are achieved and reproduced with permission from Ref. [58].

FluorophoreNanotheranostics inline graphic(in PBS)Absorption [nm]Emission [nm]Ref.
ICG0.042777802[54, 55]
Alexa Fluor 7500.12749775[56]
IRDye 800CW0.12774789[57]

In addition to contrast-enhanced imaging, various functionalized nanoparticles have been investigated for visualization of biological conditions in vivo [59-61]. By synthesizing with the targeting function, the nanoparticles can specifically interact with the target, thus can visualize functional procedures of biological systems, such as tumor growth [62-64], lymphatic drainage [65], and whole-body distribution of drugs [66].

Multispectral Fluorescence Imaging of Nanoparticles

FLI with FL nanoparticles has been widely applied for monitoring and tracking the biodistribution of agents in real-time [67-69]. In particular, the study of FLI with the excitation of near-infrared (NIR) light sources has been used for whole-body imaging since the photon scattering of NIR light is less than that in other wavelength regions. In general, the emitted fluorescence signals are mixed with the autofluorescence from the tissue, and it prevents obtaining clear images from the biological tissue. However, in multispectral FLI, it is possible to differentiate the FL signals of various probes by analyzing the response from different wavelengths. Recently, several studies using multispectral FLI had been conducted for preclinical and clinical applications including sensitive tumor labeling [70], monitoring drug delivery [71, 72], and image-guided surgery [73-75]. Recently, several examples of in vivo multispectral FLI have been reported using FL nanoparticles.

At the early stage of multispectral FLI, Kobayashi et al. reported the multispectral FLI of lymphatic networks using five different NIR-FL probes [66]. In the following study, they synthesized quantum dots (QDs) for the same purpose [76]. Leveraging the nature of QDs whose absorption spectrum varies with size, they developed five different carboxyl-QDs with absorption peaks at 565, 605, 655, 705, and 800 nm, respectively (Fig. 3A). To validate the feasibility of contrast-enhanced imaging of QDs in vivo, they intracutaneously injected the five QDs into five different sites in mice (Fig. 3B). The multispectral FLI results showed that the five QDs were separately delivered to corresponding lymph nodes that matched with the anatomy of the lymphatic system in the upper body of the mouse (Fig. 3C). From the multispectral analysis, the accumulations of five QDs in the corresponding lymph nodes were successfully differentiated. The result showed the great potential of multispectral FLI to be used in multi-color lymphangiography.

In 2012, Han et al. introduced FLI-guided tumor detection and drug delivery using gold-doped CdHgTe QDs (Au:CdHgTe QDs) [77]. They synthesized three different types of nanoparticles by conjugating arginine-glycine-aspartic acid (RGD) peptide, anti-epidermal growth factor receptor (anti-EGFR) monoclonal antibody (MAb), and anti-carcinoembryonic antigen-related cell adhesion molecule-1 (anti-CEACAM1) MAb separately. The three types of conjugates (i.e., QD800-RGD, QD820-anti-CEACAM1, and QD840-anti-EGFR) were simultaneously detected in vivo, especially showed great potential to be used for tumor targeting agents with specific delineation of tumor region (Fig. 3D). The multispectral FLI results verified the feasibility of the bioconjugated QDs for tumor targeting by comparing them with the FLI results of control mice. The mixtures of QDs were intravenously injected into human lung epithelial carcinoma xenografts in nude mice. In the results, the primary tumor, metastatic tumor, and lymphatic basin were delineated from the multispectral analysis of images (Fig 3E and 3F).

Xiang et al. proposed another QD-based nanoparticle that targets Ki-67 and human epidermal growth factor receptor-2 (HER2) [78]. Since these antigens are expressed in large amounts during breast cancer manifestation, the malignant breast cancer cells could have been quantitatively studied by injecting the targeted nanoparticles. Figure 3G shows the multispectral fluorescence signals expressed on the surface of the target cells. Ki-67 was represented in red, while HER2 was in green. While the selection of FL probes is important for sensitive tumor detection and drug delivery monitoring, there was another study that has improved the accuracy of signal detection improving an endoscope system. Bae, et al. proposed a multispectral molecular imaging endoscopy system to acquire multispectral FLI of colon dysplasia affected areas, equipped with a liquid crystal tunable filter with a wavelength range of 420~720 nm [79]. The system removes the autofluorescence of the lesion of interest by separating the multispectral signals, thus can successfully describe the colon dysplasia (Fig. 3H).

 Figure 3 

Representative results of multispectral FLI using fluorescent nanoparticles. (A) Emission spectra of five carboxyl QDs for contrast-enhanced lymph node imaging. (B) Schematic illustration of the injection site and the anatomy of the lymphatic system and the injection. Blue dashed box depicts imaging region. (C) The overlaid in vivo image of multispectral FLI and WLI after injection of the five carboxyl QDs. (D) The overlaid in vivo images of multispectral FLI and WLI from the human lung epithelial carcinoma xenografts in nude mice. (E) Region of interests for multispectral analysis. (F) Quantified unmixed signal in each region of interest. (G) Multispectral FLI of Ki67 and HER2 co-expressions in breast cancer cells. (H) In vivo WLI, multispectral FLI, and overlaid images of polyps using fluorescent probes. FLI, fluorescence imaging; WLI, white light imaging; QD, quantum dot; NLN, neck lymph node; LTLN, lateral thoracic lymph node; ALN, axillary lymph node; PT, primary tumor; MT, metastatic tumor; LB, lymphatic basin; RGD, arginine-glycine-aspartic acid; anti-CEACAM1, anti-carcinoembryonic antigen-related cell adhesion molecule-1; anti-EGFR, anti-epidermal growth factor receptor; HER2, human epidermal growth factor receptor-2. The images are reproduced with permission from Refs. [76-79].

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Multispectral Two-Photon Microscopy of Nanoparticles

The most distinguishable feature of TPM compared to FLI is the two-photon excitation by light sources with longer wavelengths in the NIR region. Since the excitation occurs in the limited region of the focal point, which has a typical volume of a few femtoliters, TPM can achieve 3D images of high sensitivity and submicron resolution without using a confocal pinhole [80]. In addition, deeper penetration of light in biological tissues (0.6 ~ 0.8 mm) is possible because of the reduced absorption and scattering of the longer wavelengths [81, 82]. As two-photon emission is a non-linear process with a small cross-section, high photon flux is required to generate high efficiency in the process, which is typically achieved through ultrashort pulsed lasers. At each pulse of light, the number of photons absorbed in a sample is defined as follows [83].

Nanotheranostics inline graphic  (7) 

where Nanotheranostics inline graphic is the average power of the light source, Nanotheranostics inline graphic is the two-photon absorption rate of the fluorophore at the wavelength (Nanotheranostics inline graphic), Nanotheranostics inline graphic is the pulse duration of the light source, Nanotheranostics inline graphic is the repetition rate of the light source, Nanotheranostics inline graphic is the numerical aperture of the objective lens, Nanotheranostics inline graphic is Planck's constant, and Nanotheranostics inline graphic is the speed of light. From the equation, the shorter pulse duration leads to a higher probability of two-photon absorption when the average power is considered constant. Therefore, ultrashort (typically ~140 fs) pulsed laser has widely been used for TPM. The ultrashort laser pulse also reduces the photodamage to the biological sample, thus can be used for in vivo imaging of live samples. Moreover, multispectral TPM can identify the composition of biological tissues labeled with several FL nanoparticles. Recently, multispectral analyses of nanoparticles using TPM have been explored for applications including therapeutic process [84, 85], cell tracking optical probe [86-88], the morphogenetic process of neurons [89, 90], and functional analysis to reveal disease progression at the cellular level [91-93].

 Figure 4 

Representative results of multispectral TPM using FL nanoparticles. (A) Multicolor TPM of A549 and MCF-7 cells using multi-emission FL nanoparticles. (B) Multicolor TPM images of MRSA using aptamer-modified GO sheets with various excitation wavelenghts. White circles depict the positions of MRSAs. (C) TPM images of a xenografted melanoma in a mouse ear before and after injection of Dylihgt 488 conjugated nanoparticles. TPM, two-photon microscopy; FL, fluorescent; MRSA, methicillin-resistant Staphylococcus aureus; SHG, second harmonic generation. The images are reproduced with permission from Refs. [96, 98, 99].

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FL nanoparticles also have widely been used in TPM. To achieve high efficiency of FL light emission, the nanoparticles are typically synthesized from the aggregated fluorophores because they have large stroke shifts caused by excited-state intramolecular proton transfer (ESIPT) molecules [94, 95]. In 2014, Deng et al. demonstrated the two-photon absorption of FL nanoparticles derived from several salicylidenealiline molecules [96], which are well-known molecules that demonstrate the ESIPT phenomenon [97]. They achieved multicolor TPM images of human alveolar basal epithelial (A549) and breast cancer (MCF-7) cells under the excitation wavelength of 405 nm (Fig. 4A). The results showed the feasibility of multispectral TPM as a promising platform for multicolor cell imaging applications.

Pramanik et al. reported an aptamer conjugated graphene oxide (GO), which can be used for multiple drug-resistance bacteria (MDRB) imaging [98]. They found that the emission wavelength of the aptamer conjugated GO was tunable from visible to NIR by varying excitation wavelength, without changing its chemical properties or size (Fig. 4B). They demonstrated the multicolor TPM images of methicillin-resistant Staphylococcus aureus (MRSA) in the aptamer conjugated graphene oxide nanosheets. The nanoparticles have efficient two-photon emission with two-photon excitation through the wavelengths of 760, 880, 980, and 1160 nm. By demonstrating the high efficiency of two-photon excitation, photo-stability, and biocompatibility, the results showed the feasibility of multispectral TPM of GO nanoparticles for delineating the multiple MDRBs.

TPM also has been utilized for multicolor tumor imaging from the uptaken nanoparticles in tumor cells. Roode et al. achieved multispectral TPM images from a xenografted melanoma tumor in the ear dermis of mice [99]. They used particle replication in the non-wetting templates (PRINT) technique to produce uniformly sized nanoparticles. They investigated the tumor uptake of the PRINT-nanoparticles by simultaneously acquiring TPM images of the tumor (tdTomato) and the FL nanoparticles (Dylight488). They also acquired the second harmonic generation (SHG) signal which can detect the signals from the bundled collagen (Fig. 4C). The results showed the potential of the multispectral TPM for analyzing the further in-depth correlation between the characteristics of nanoparticles and tumor cells.

Multispectral Photoacoustic Imaging of Nanoparticles

In contrast to the pure optical imaging techniques, where the imaging depth is greatly limited by strong photon scattering in biological tissues, PAI allows deeper imaging depth because the signal is transported through acoustic waves that are less scattered in biological tissues compared to the photon. Although the signal is delivered as a form of the acoustic wave in PAI, the generation of the signal is based on the optical absorption, which enables PAI can be used for multispectral analysis by tuning the wavelength of the illumination light source. Several endogenous chromophores such as oxy-hemoglobin, deoxy-hemoglobin, melanin, and lipid, PAI can provide both functional and structural information of biological tissues [100-102]. In addition to endogenous imaging, contrast-enhanced PAI has widely been investigated by using various exogenous nanoparticles with functionalities of contrast enhancement, disease targeting, or drug delivery [103-106].

Zhang et al. introduced naphthalocyanine nanoparticles (NNs) that have stable optical absorption spectra with controllable absorption peaks (Fig. 5A) [107]. They showed the feasibility of contrast-enhanced PAI with an application of the gastrointestinal tract of mice in vivo. The NNs were injected by oral administration, then the distribution of the nanoparticles through the gastrointestinal tract was successfully visualized (Fig. 5B). In the following study, Lee et al. delineated multiple lymphatic paths by multispectral PA analysis of mice in vivo [108]. They subcutaneously injected two different NNs (absorption peaks at 707 and 863 nm, respectively) at each side of the forepaw, acquired multispectral PA images, visualized lymphatic drainage by overlaying unmixed PA signals (Fig. 5C). The results show the potential of nanoparticles for multispectral analysis of contrast-enhanced PA images in vivo.

In 2016, Gurka et al. showed improved pancreatic tumor imaging using mesoporous silica nanoparticles (MSNs) [109]. They added chitosan and urokinase plasminogen activator (UPA) receptors to the nanoparticles for targeting the acidic tumor microenvironment and overexpressed receptors in tumors, respectively. In addition, indocyanine green was loaded for multispectral PAI. They acquired multispectral PA images of pancreatic cancer (S2VP10 cell line) bearing mice in vivo, with wavelengths of 680, 710, 730, 740, 760, 770, 780, 800, 850, and 900 nm. The spectrally unmixed PA signals show that the UPA-added MSNs (MSN-UPAs) accumulates more in the pancreatic tumor compared to the pure MSNs (Fig. 5D). The results show the illustration of the targeting efficacy of nanoparticles, which can be utilized for a variety of studies in drug delivery and disease identification.

Over the past few decades, gold nanoparticles have gained much attention for contrast-enhanced imaging due to their excellent optical absorption, easiness of synthesis, and chemical stability [110]. Liu et al. demonstrated the contrast-enhanced tumor images using an FL dye (Alexa Fluor Dye680) conjugated gold nanocages (GNCs), especially for tumor protease detection in 2018 [111]. Tumor protease is one of the important factors controlling tumor proliferation, thus it is useful to identify the degree of tumor activation. The synthesized GNC-peptide- FL dyes (GPDs) were targeted to the MMP-2 protease through the enzymatic peptide substrate. When the peptide substrate was cleaved after combining with MMP-2, a distinct chemical change of tumor protease signal was detected from glioblastoma xenografts in nude mice in vivo (Fig. 5E). As the time flows, the PA signals from the uncleaved GPDs (green in Fig. 5E) decreased while the PA signals from the cleaved GPDs (red in Fig. 5E) increased. The results show the feasibility of multispectral PA for monitoring chemical response in biological tissues in vivo.

 Figure 5 

Representative results of multispectral PAI using contrast-enhancing nanoparticles. (A) Optical absorption spectra of four NNs for contrast-enhanced PAI. Numbers in the photograph represent the absorption peak of each NN. (B) Contrast-enhanced PA image of gastrointestinal tract of a NN-injected mouse in vivo. (C) Delineation of axillary lymphatic networks from in vivo multispectral contrast-enhanced PA images. (D) Unmixed ICG images showing nanoparticle accumulation in pancreatic tumor in vivo. (E) Multispectral PA images of glioblastoma after intravascular injection of GPD probes. PAI, photoacoustic imaging; PA, photoacoustic; NN, naphthalocyanine nanoparticle; LN, lymph node; LV, lymphatic vessel; ICG, indocyanine green; MSN, mesoporous silica nanoparticle; UPA. urokinase plasminogen activator; P, pancreas; S, spleen; K, kidney; GPD, gold nanocage-peptide-fluorescent dye. The images are reproduced with permission from Refs. [107-109, 111]

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 Table 2 

Performance benchmarks and biomedical applications of imaging systems that used multispectral analysis of nanoparticles. fluorescence imaging; TPM, two-photon microscopy; PAI, photoacoustic imaging. N/A, not available.

RefImaging modalityModelSpatial resolutionImaging depthImaging speedApplications
[76]FLIMaestro(CRi)25 μmN/A10 secLymph node mapping
[77]FLIMaestro(CRi)25 μmN/A10 secWhole-body distribution mapping
[78]FLINuance(CRi)~1 μmN/A~5 secBreast cancer cell imaging, Cell identification
[79]FLINuance(CRi)~1 μmN/A~5 secEndoscopic imaging of polyps in mice colon
[96]TPMN/AN/AN/AN/ABreast cancer cell imaging, Cell identification
[98]TPMFV1000MPE(Olympus)~1 μm320 μm16 fpsAggregation monitoring of
MRSA bacteria in aptamer
[99]TPMFV1000MPE(Olympus)~1 μm320 μm16 fpsMelanoma imaging,Particle uptaken assessment
[107]PAICustom [41]590 μm~10.3 mm~20 minGastrointestinal track monitoring,Detection of small bowel obstraction
[108]PAICustom [41]590 μm~10.3 mm~20 minLymph node mapping
[109]PAIinVision 256TF(iThera Medical)150 μm~10 mm10 fpsAccumulation monitoring of particles in pancreatic tumor
[111]PAIVevo2100 LAZR(VisualSonics)N/A~5 mm20 fpsAccumulation monitoring of particles in glioblastoma

Summary and Conclusion

Multispectral imaging techniques are the methods that detect and classify features. The underlying concept of the technique is the spectral unmixing of the signals based on the spectral responses of chromophores. In this review, we summarized the basic principles of representative multispectral imaging techniques, then explored their applications in biomedical studies (Table 2). The contrast-enhanced images from the administration of nanoparticles enable the multispectral analysis to differentiate lymphatic networks, delineate diseased regions, and monitor the chemical changes in biological tissues. The representative results show the feasibility of the multispectral analysis of nanoparticles in the exploration of anatomy, biochemistry, pathology, and physiology in preclinical biomedical engineering. As potential clinical diagnosing tools, multispectral imaging systems have been used to monitor biological changes in vivo by delivering a variety of nanoparticles. To expand the application area to the clinical world, several challenges should be addressed in developing the nanoparticle including reducing toxicity, ensuring biocompatibility, enhancing biodegradability, and improving photostability. In summary, the multispectral analysis of nanoparticles has great potential to be used in a variety of preclinical and clinical biomedical researches. The continuous efforts by researchers to improve the system configuration for achieving a higher signal-to-noise ratio, a better spatiotemporal resolution, and a deeper imaging depth would expand the application areas of the multispectral imaging techniques. Therefore, the spectral imaging of nanoparticles would become an essential tool for biological and biomedical studies.


This work was supported by a 2-Year Research Grant of Pusan National University.

Competing Interests

The authors have declared that no competing interest exists.


1. Kagadis GC, Loudos G, Katsanos K, Langer SG, Nikiforidis GC. In vivo small animal imaging: current status and future prospects. Medical physics. 2010;37:6421-42

2. Holdsworth DW, Thornton MM. Micro-CT in small animal and specimen imaging. Trends in Biotechnology. 2002;20:S34-S9

3. Schambach SJ, Bag S, Schilling L, Groden C, Brockmann MA. Application of micro-CT in small animal imaging. Methods. 2010;50:2-13

4. Ritman EL. Current status of developments and applications of micro-CT. Annual review of biomedical engineering. 2011;13:531-52

5. Maramraju SH, Smith SD, Junnarkar SS, Schulz D, Stoll S, Ravindranath B. et al. Small animal simultaneous PET/MRI: initial experiences in a 9.4 T microMRI. Physics in medicine and biology. 2011;56:2459

6. Judenhofer MS, Cherry SR. Applications for preclinical PET/MRI. Seminars in nuclear medicine: Elsevier. 2013 p. 19-29

7. Kersemans V, Thompson J, Cornelissen B, Woodcock M, Allen PD, Buls N. et al. Micro-CT for anatomic referencing in PET and SPECT: radiation dose, biologic damage, and image quality. Journal of Nuclear Medicine. 2011;52:1827-33

8. Nuyts J, Vunckx K, Defrise M, Vanhove C. Small animal imaging with multi-pinhole SPECT. Methods. 2009;48:83-91

9. Foster FS, Hossack J, Adamson SL. Micro-ultrasound for preclinical imaging. Interface focus. 2011;1:576-601

10. Needles A, Arditi M, Rognin N, Mehi J, Coulthard T, Bilan-Tracey C. et al. Nonlinear contrast imaging with an array-based micro-ultrasound system. Ultrasound in medicine & biology. 2010;36:2097-106

11. Greco A, Mancini M, Gargiulo S, Gramanzini M, Claudio P, Brunetti A. et al. Ultrasound biomicroscopy in small animal research: applications in molecular and preclinical imaging. Journal of Biomedicine and Biotechnology. 2012. 2012

12. Luker GD, Luker KE. Optical imaging: current applications and future directions. Journal of Nuclear Medicine. 2008;49:1-4

13. Pawley J. Handbook of biological confocal microscopy: Springer Science & Business Media; 2006

14. Steinberg I, Kim J, Schneider MK, Hyun D, Zlitni A, Hooper SM. et al. Superiorized Photo-Acoustic Non-NEgative Reconstruction (SPANNER) for Clinical Photoacoustic Imaging. IEEE Transactions on Medical Imaging. 2021

15. Olefir I, Tzoumas S, Restivo C, Mohajerani P, Xing L, Ntziachristos V. Deep Learning-Based Spectral Unmixing for Optoacoustic Imaging of Tissue Oxygen Saturation. IEEE transactions on medical imaging. 2020;39:3643-54

16. Vasefi F, MacKinnon N, Farkas D. Hyperspectral and multispectral imaging in dermatology. Imaging in Dermatology: Elsevier. 2016 p. 187-201

17. Dickinson M, Bearman G, Tille S, Lansford R, Fraser S. Multi-spectral imaging and linear unmixing add a whole new dimension to laser scanning fluorescence microscopy. Biotechniques. 2001;31:1272-8

18. Themelis G, Yoo JS, Ntziachristos V. Multispectral imaging using multiple-bandpass filters. Optics letters. 2008;33:1023-5

19. Phanse Y, Ramer-Tait AE, Friend SL, Carrillo-Conde B, Lueth P, Oster CJ. et al. Analyzing cellular internalization of nanoparticles and bacteria by multi-spectral imaging flow cytometry. Journal of visualized experiments: JoVE. 2012

20. Halig LV, Wang D, Wang AY, Chen ZG, Fei B. Biodistribution study of nanoparticle encapsulated photodynamic therapy drugs using multispectral imaging. Medical Imaging 2013: Biomedical Applications in Molecular, Structural, and Functional Imaging: International Society for Optics and Photonics. 2013 p. 867218

21. Zhan C, Huang Y, Lin G, Huang S, Zeng F, Wu S. A Gold Nanocage/Cluster Hybrid Structure for Whole-Body Multispectral Optoacoustic Tomography Imaging, EGFR Inhibitor Delivery, and Photothermal Therapy. Small. 2019;15:1900309

22. Graves E, Weissleder R, Ntziachristos V. Fluorescence molecular imaging of small animal tumor models. Current molecular medicine. 2004;4:419-30

23. Graves EE, Ripoll J, Weissleder R, Ntziachristos V. A submillimeter resolution fluorescence molecular imaging system for small animal imaging. Medical physics. 2003;30:901-11

24. Wang K, He X, Yang X, Shi H. Functionalized silica nanoparticles: a platform for fluorescence imaging at the cell and small animal levels. Accounts of chemical research. 2013;46:1367-76

25. Kim C, Favazza C, Wang LV. In Vivo Photoacoustic Tomography of Chemicals: High-Resolution Functional and Molecular Optical Imaging at New Depths. Chemical Reviews. 2010;110:2756-82

26. Kim J, Park E-Y, Park B, Choi W, Lee KJ, Kim C. Towards Clinical Photoacoustic and Ultrasound Imaging: Probe Improvement and Real-Time Graphical User Interface. Experimental Biology and Medicine. 2020;245:321-9

27. Steinberg I, Huland DM, Vermesh O, Frostig HE, Tummers WS, Gambhir SS. Photoacoustic Clinical Imaging. Photoacoustics. 2019;14:77-98

28. Choi W, Park E-Y, Jeon S, Kim C. Clinical photoacoustic imaging platforms. Biomedical Engineering Letters. 2018:1-17

29. Kim J, Park S, Jung Y, Chang S, Park J, Zhang Y. et al. Programmable Real-time Clinical Photoacoustic and Ultrasound Imaging System. Sci Rep. 2016;6:35137

30. Lin L, Hu P, Shi J, Appleton CM, Maslov K, Li L. et al. Single-Breath-Hold Photoacoustic Computed Tomography of the Breast. Nature Communications. 2018;9:2352

31. Toi M, Asao Y, Matsumoto Y, Sekiguchi H, Yoshikawa A, Takada M. et al. Visualization of tumor-related blood vessels in human breast by photoacoustic imaging system with a hemispherical detector array. Scientific reports. 2017;7:41970

32. Heijblom M, Steenbergen W, Manohar S. Clinical Photoacoustic Breast Imaging: The Twente experience. Pulse, IEEE. 2015;6:42-6

33. Roll W, Markwardt NA, Masthoff M, Helfen A, Claussen J, Eisenblätter M. et al. Multispectral Optoacoustic Tomography of Benign and Malignant Thyroid Disorders - A Pilot Study. Journal of Nuclear Medicine. 2019;60:1461-6

34. Kroenke M, Karlas A, Fasoula N, Markwardt N, Scheidhauer K, Eiber M. et al. Multispectral Optoacoustic Tomography: A Novel Label-Free Imaging Technique for the Assessment of hyperthyroid diseases. Journal of Nuclear Medicine. 2019;60:525 -

35. Yang M, Zhao L, He X, Su N, Zhao C, Tang H. et al. Photoacoustic/Ultrasound Dual Imaging of Human Thyroid Cancers: An Initial Clinical Study. Biomedical Optics Express. 2017;8:3449-57

36. Kim J, Kim M-H, Jo K, Ha J, Kim Y, Lim D-J. et al. Photoacoustic analysis of thyroid cancer in vivo: a pilot study. Photons Plus Ultrasound: Imaging and Sensing 2017: International Society for Optics and Photonics. 2017 p. 1006408

37. Kothapalli S-R, Sonn GA, Choe JW, Nikoozadeh A, Bhuyan A, Park KK. et al. Simultaneous transrectal ultrasound and photoacoustic human prostate imaging. Science Translational Medicine. 2019;11:eaav2169

38. Park B, Bang CH, Lee C, Han JH, Choi W, Kim J. et al. 3D Wide-field Multispectral Photoacoustic Imaging of Human Melanomas In Vivo: A Pilot Study. Journal of the European Academy of Dermatology and Venereology. 2020

39. Kim J, Kim YH, Park B, Seo HM, Bang CH, Park GS. et al. Multispectral Ex Vivo Photoacoustic Imaging of Cutaneous Melanoma for Better Selection of the Excision Margin. British Journal of Dermatology. 2018;179:780-2

40. Park S, Park G, Kim J, Choi W, Jeong U, Kim C. Bi2Se3 nanoplates for contrast-enhanced photoacoustic imaging at 1064 nm. Nanoscale. 2018;10:20548-58

41. Jeon M, Kim J, Kim C. Multiplane spectroscopic whole-body photoacoustic imaging of small animals in vivo. Medical & Biological Engineering & Computing. 2014:1-12

42. Park E-Y, Park S, Lee H, Kang M, Kim C, Kim J. Simultaneous Dual-Modal Multispectral Photoacoustic and Ultrasound Macroscopy for Three-Dimensional Whole-Body Imaging of Small Animals. Photonics: Multidisciplinary Digital Publishing Institute. 2021 p. 13

43. Kim J, Park B, Ha J, Steinberg I, Hooper SM, Jeong C. et al. Multiparametric Photoacoustic Analysis of Human Thyroid Cancers In Vivo. Cancer Research. 2021

44. Lakowicz JR. Principles of fluorescence spectroscopy: Springer science & business media; 2013

45. Yuste R. Fluorescence microscopy today. Nature methods. 2005;2:902-4

46. Drummen GP. Fluorescent probes and fluorescence (microscopy) techniques—illuminating biological and biomedical research. Molecules. 2012;17:14067-90

47. Lichtman JW, Conchello J-A. Fluorescence microscopy. Nature methods. 2005;2:910-9

48. Diaspro A, Chirico G, Collini M. Two-photon fluorescence excitation and related techniques in biological microscopy. Quarterly reviews of biophysics. 2005;38:97

49. Kim J, Lee D, Jung U, Kim C. Photoacoustic imaging platforms for multimodal imaging. Ultrasonography. 2015;34:88

50. Bell AG. The photophone. Science. 1880;1:130-4

51. Park S, Lee C, Kim J, Kim C. Acoustic resolution photoacoustic microscopy. Biomedical Engineering Letters. 2014;4:213-22

52. Baik JW, Kim JY, Cho S, Choi S, Kim J, Kim C. Super Wide-field Photoacoustic Microscopy of Animals and Humans In Vivo. IEEE transactions on medical imaging. 2019

53. Rao B, Soto F, Kerschensteiner D, Wang LV. Integrated photoacoustic, confocal, and two-photon microscope. Journal of biomedical optics. 2014;19:036002 -

54. Park S, Kim J, Jeon M, Song J, Kim C. In Vivo Photoacoustic and Fluorescence Cystography Using Clinically Relevant Dual Modal Indocyanine Green. Sensors. 2014;14:19660-8

55. Kim C, Song KH, Gao F, Wang LV. Sentinel lymph nodes and lymphatic vessels: noninvasive dual-modality in vivo mapping by using indocyanine green in rats—volumetric spectroscopic photoacoustic imaging and planar fluorescence imaging 1. Radiology. 2010;255:442-50

56. Razansky D, Vinegoni C, Ntziachristos V. Multispectral photoacoustic imaging of fluorochromes in small animals. Optics letters. 2007;32:2891-3

57. Chen J, Gao Z, Li G, Wang TD. Dual-modal in vivo fluorescence and photoacoustic imaging using a heterodimeric peptide. Chemical Communications. 2018;54:13196-9

58. Chen Z, Deán-Ben XL, Gottschalk S, Razansky D. Performance of optoacoustic and fluorescence imaging in detecting deep-seated fluorescent agents. Biomedical optics express. 2018;9:2229-39

59. Koo H, Huh MS, Ryu JH, Lee D-E, Sun I-C, Choi K. et al. Nanoprobes for biomedical imaging in living systems. Nano Today. 2011;6:204-20

60. Sperling RA, Gil PR, Zhang F, Zanella M, Parak WJ. Biological applications of gold nanoparticles. Chemical Society Reviews. 2008;37:1896-908

61. Jain PK, Lee KS, El-Sayed IH, El-Sayed MA. Calculated absorption and scattering properties of gold nanoparticles of different size, shape, and composition: applications in biological imaging and biomedicine. The Journal of Physical Chemistry B. 2006;110:7238-48

62. Wang L, Xia Q, Liu R, Qu J. A red fluorescent probe for ribonucleic acid (RNA) detection, cancer cell tracing and tumor growth monitoring. Sensors and Actuators B: Chemical. 2018;273:935-43

63. Liu J, Li K, Liu B. Far-red/near-infrared conjugated polymer nanoparticles for long-term in situ monitoring of liver tumor growth. Advanced Science. 2015;2:1500008

64. Zhang Q, Iwakuma N, Sharma P, Moudgil B, Wu C, McNeill J. et al. Gold nanoparticles as a contrast agent for in vivo tumor imaging with photoacoustic tomography. Nanotechnology. 2009;20:395102

65. Ballou B, Ernst LA, Andreko S, Harper T, Fitzpatrick JA, Waggoner AS. et al. Sentinel lymph node imaging using quantum dots in mouse tumor models. Bioconjugate chemistry. 2007;18:389-96

66. Kobayashi H, Koyama Y, Barrett T, Hama Y, Regino CA, Shin IS. et al. Multimodal nanoprobes for radionuclide and five-color near-infrared optical lymphatic imaging. ACS nano. 2007;1:258-64

67. Ruan G, Agrawal A, Marcus AI, Nie S. Imaging and tracking of tat peptide-conjugated quantum dots in living cells: new insights into nanoparticle uptake, intracellular transport, and vesicle shedding. Journal of the American Chemical Society. 2007;129:14759-66

68. Balzarotti F, Eilers Y, Gwosch KC, Gynnå AH, Westphal V, Stefani FD. et al. Nanometer resolution imaging and tracking of fluorescent molecules with minimal photon fluxes. Science. 2017;355:606-12

69. Lien Z-Y, Hsu T-C, Liu K-K, Liao W-S, Hwang K-C, Chao J-I. Cancer cell labeling and tracking using fluorescent and magnetic nanodiamond. Biomaterials. 2012;33:6172-85

70. Kamiya M, Kobayashi H, Hama Y, Koyama Y, Bernardo M, Nagano T. et al. An enzymatically activated fluorescence probe for targeted tumor imaging. Journal of the American Chemical Society. 2007;129:3918-29

71. Etrych T, Lucas H, Janoušková O, Chytil P, Mueller T, Mäder K. Fluorescence optical imaging in anticancer drug delivery. Journal of Controlled Release. 2016;226:168-81

72. Ghaderi S, Ramesh B, Seifalian AM. Fluorescence nanoparticles “quantum dots” as drug delivery system and their toxicity: a review. Journal of drug targeting. 2011;19:475-86

73. Mery E, Golzio M, Guillermet S, Lanore D, Le Naour A, Thibault B. et al. Fluorescence-guided surgery for cancer patients: a proof of concept study on human xenografts in mice and spontaneous tumors in pets. Oncotarget. 2017;8:109559

74. Nguyen QT, Tsien RY. Fluorescence-guided surgery with live molecular navigation—a new cutting edge. Nature reviews cancer. 2013;13:653-62

75. Nagaya T, Nakamura YA, Choyke PL, Kobayashi H. Fluorescence-guided surgery. Frontiers in oncology. 2017;7:314

76. Kobayashi H, Hama Y, Koyama Y, Barrett T, Regino CA, Urano Y. et al. Simultaneous multicolor imaging of five different lymphatic basins using quantum dots. Nano Letters. 2007;7:1711-6

77. Han S, Mu Y, Zhu Q, Gao Y, Li Z, Jin Q. et al. Au: CdHgTe quantum dots for in vivo tumor-targeted multispectral fluorescence imaging. Analytical and bioanalytical chemistry. 2012;403:1343-52

78. Xiang Q-M, Wang L-W, Yuan J-P, Chen J-M, Yang F, Li Y. Quantum dot-based multispectral fluorescent imaging to quantitatively study co-expressions of Ki67 and HER2 in breast cancer. Experimental and molecular pathology. 2015;99:133-8

79. Bae SM, Bae D-J, Do E-J, Oh G, Yoo SW, Lee G-J. et al. Multi-spectral fluorescence imaging of colon dysplasia in vivo using a multi-spectral endoscopy system. Translational oncology. 2019;12:226-35

80. Denk W, Strickler JH, Webb WW. Two-photon laser scanning fluorescence microscopy. Science. 1990;248:73-6

81. Helmchen F, Denk W. Deep tissue two-photon microscopy. Nature methods. 2005;2:932-40

82. Campagnola PJ, Lewis A, Loew LM. High-resolution nonlinear optical imaging of live cells by second harmonic generation. Biophysical journal. 1999;77:3341-9

83. So PT, Dong CY, Masters BR, Berland KM. Two-photon excitation fluorescence microscopy. Annual review of biomedical engineering. 2000;2:399-429

84. Park YI, Lee KT, Suh YD, Hyeon T. Upconverting nanoparticles: a versatile platform for wide-field two-photon microscopy and multi-modal in vivo imaging. Chemical Society Reviews. 2015;44:1302-17

85. Wu Y-X, Zhang D, Hu X, Peng R, Li J, Zhang X. et al. Multicolor Two-photon Nanosystem for Multiplexed Intracellular Imaging and Targeted Cancer Therapy. Angewandte Chemie. 2021

86. Rampazzo E, Boschi F, Bonacchi S, Juris R, Montalti M, Zaccheroni N. et al. Multicolor core/shell silica nanoparticles for in vivo and ex vivo imaging. Nanoscale. 2012;4:824-30

87. Pecher J, Huber J, Winterhalder M, Zumbusch A, Mecking S. Tailor-made conjugated polymer nanoparticles for multicolor and multiphoton cell imaging. Biomacromolecules. 2010;11:2776-80

88. Chen C, Wang F, Wen S, Su QP, Wu MC, Liu Y. et al. Multi-photon near-infrared emission saturation nanoscopy using upconversion nanoparticles. Nature communications. 2018;9:1-6

89. Serduc R, Vérant P, Vial J-C, Farion R, Rocas L, Rémy C. et al. In vivo two-photon microscopy study of short-term effects of microbeam irradiation on normal mouse brain microvasculature. International Journal of Radiation Oncology* Biology* Physics. 2006;64:1519-27

90. Patel KD, Singh RK, Kim H-W. Carbon-based nanomaterials as an emerging platform for theranostics. Materials Horizons. 2019;6:434-69

91. Dunn KW, Sandoval RM, Kelly KJ, Dagher PC, Tanner GA, Atkinson SJ. et al. Functional studies of the kidney of living animals using multicolor two-photon microscopy. American Journal of Physiology-Cell Physiology. 2002;283:C905-C16

92. Ueki H, Wang I-H, Zhao D, Gunzer M, Kawaoka Y. Multicolor two-photon imaging of in vivo cellular pathophysiology upon influenza virus infection using the two-photon IMPRESS. Nature protocols. 2020;15:1041-65

93. Kim H, Park Y, Beack S, Han S, Jung D, Cha HJ. et al. Dual-color-emitting carbon nanodots for multicolor bioimaging and optogenetic control of ion channels. Advanced science. 2017;4:1700325

94. Liu Y, Deng C, Tang L, Qin A, Hu R, Sun JZ. et al. Specific detection of D-glucose by a tetraphenylethene-based fluorescent sensor. Journal of the American Chemical Society. 2011;133:660-3

95. Tang K-C, Chang M-J, Lin T-Y, Pan H-A, Fang T-C, Chen K-Y. et al. Fine tuning the energetics of excited-state intramolecular proton transfer (ESIPT): white light generation in a single ESIPT system. Journal of the American Chemical Society. 2011;133:17738-45

96. Deng H, Liu B, Yang C, Li G, Zhuang Y, Li B. et al. Multi-color cell imaging under identical excitation conditions with salicylideneaniline analogue-based fluorescent nanoparticles. RSC Advances. 2014;4:62021-9

97. Hadjoudis E, Mavridis IM. Photochromism and thermochromism of Schiff bases in the solid state: structural aspects. Chemical Society Reviews. 2004;33:579-88

98. Pramanik A, Fan Z, Chavva SR, Sinha SS, Ray PC. Highly efficient and excitation tunable two-photon luminescence platform for targeted multi-color MDRB imaging using graphene oxide. Scientific reports. 2014;4:1-6

99. Roode LE, Brighton H, Bo T, Perry JL, Parrott MC, Kersey F. et al. Subtumoral analysis of PRINT nanoparticle distribution reveals targeting variation based on cellular and particle properties. Nanomedicine: Nanotechnology, Biology and Medicine. 2016;12:1053-62

100. Zhou Y, Tripathi SV, Rosman I, Ma J, Hai P, Linette GP. et al. Noninvasive determination of melanoma depth using a handheld photoacoustic probe. Journal of Investigative Dermatology. 2017;137:1370-2

101. Lee C, Jeon M, Jeon MY, Kim J, Kim C. In vitro photoacoustic measurement of hemoglobin oxygen saturation using a single pulsed broadband supercontinuum laser source. Applied Optics. 2014;53:3884-9

102. Wang X, Stoica G, Xie X, Ku G, Wang LV. Noninvasive imaging of hemoglobin concentration and oxygenation in the rat brain using high-resolution photoacoustic tomography. Journal of biomedical optics. 2006;11:024015-9

103. Noh I, Kim M, Kim J, Lee D, Oh D, Kim J. et al. Structure-inherent near-infrared bilayer nanovesicles for use as photoacoustic image-guided chemo-thermotherapy. Journal of Controlled Release. 2020;320:283-92

104. Park B, Lee KM, Park S, Yun M, Choi H-J, Kim J. et al. Deep tissue photoacoustic imaging of nickel (II) dithiolene-containing polymeric nanoparticles in the second near-infrared window. Theranostics. 2020;10:2509

105. Zhou Y, Wang D, Zhang Y, Chitgupi U, Geng J, Wang Y. et al. A phosphorus phthalocyanine formulation with intense absorbance at 1000 nm for deep optical imaging. Theranostics. 2016;6:688

106. Chitgupi U, Nyayapathi N, Kim J, Wang D, Sun B, Li C. et al. Surfactant-Stripped Micelles for NIR-II Photoacoustic Imaging through 12 cm of Breast Tissue and Whole Human Breasts. Advanced Materials. 2019: 1902279.

107. Zhang Y, Jeon M, Rich LJ, Hong H, Geng J, Zhang Y. et al. Non-Invasive Multimodal Functional Imaging of the Intestine with Frozen Micellar Naphthalocyanines. Nature Nanotechnology. 2014;9:631-8

108. Lee C, Kim J, Zhang Y, Jeon M, Liu C, Song L. et al. Dual-color photoacoustic lymph node imaging using nanoformulated naphthalocyanines. Biomaterials. 2015;73:142-8

109. Gurka MK, Pender D, Chuong P, Fouts BL, Sobelov A, McNally MW. et al. Identification of pancreatic tumors in vivo with ligand-targeted, pH responsive mesoporous silica nanoparticles by multispectral optoacoustic tomography. Journal of controlled release. 2016;231:60-7

110. Alkilany AM, Murphy CJ. Toxicity and cellular uptake of gold nanoparticles: what we have learned so far?. Journal of nanoparticle research. 2010;12:2313-33

111. Liu C, Li S, Gu Y, Xiong H, Wong W-t, Sun L. Multispectral photoacoustic imaging of tumor protease activity with a gold nanocage-based activatable probe. Molecular imaging and biology. 2018;20:919-29

Author contact

Corresponding address Corresponding authors: Jeesu Kim, Ph.D., Department of Cogno-Mechatronics Engineering, College of Nanoscience & Nanotechnology, Pusan National University, 63-2 Busandaehag-Ro, Geumjeong-Gu, Busan 46241, Republic of Korea. Phone: +82-51-510-6128; Fax: +82-51-514-2358; E-mail: Chang-Seok Kim, Ph.D., Department of Cogno-Mechatronics Engineering, College of Nanoscience & Nanotechnology, Pusan National University, 63-2 Busandaehag-Ro, Geumjeong-Gu, Busan 46241, Republic of Korea. Phone: +82-51-510-6116; Fax: +82-51-514-2358; E-mail: Hyung-Hoi Kim, Ph.D., Department of Laboratory Medicine and Biomedical Research Institute, Pusan National University Hospital and Pusan National University School of Medicine, 179 Gudeok-Ro, Seo-Gu, Busan 49241, Republic of Korea. Phone: +82-51-240-7414; Fax: +82-51-510-8153; E-mail:

Received 2021-5-27
Accepted 2021-7-11
Published 2022-1-1

Citation styles

Lee, H., Kim, J., Kim, H.H., Kim, C.S., Kim, J. (2022). Review on Optical Imaging Techniques for Multispectral Analysis of Nanomaterials. Nanotheranostics, 6(1), 50-61.

Lee, H.; Kim, J.; Kim, H.H.; Kim, C.S.; Kim, J. Review on Optical Imaging Techniques for Multispectral Analysis of Nanomaterials. Nanotheranostics 2022, 6 (1), 50-61. DOI: 10.7150/ntno.63222.

Lee H, Kim J, Kim HH, Kim CS, Kim J. Review on Optical Imaging Techniques for Multispectral Analysis of Nanomaterials. Nanotheranostics 2022; 6(1):50-61. doi:10.7150/ntno.63222.

Lee H, Kim J, Kim HH, Kim CS, Kim J. 2022. Review on Optical Imaging Techniques for Multispectral Analysis of Nanomaterials. Nanotheranostics. 6(1):50-61.

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