4 January 2016 Review on photoacoustic imaging of the brain using nanoprobes
Author Affiliations +
Photoacoustic (PA) tomography (PAT) is a hybrid imaging modality that integrates rich optical contrasts with a high-ultrasonic spatial resolution in deep tissue. Among various imaging applications, PA neuroimaging is becoming increasingly important as it nicely complements the limitations of conventional neuroimaging modalities, such as the low-temporal resolution in magnetic resonance imaging and the low depth-to-resolution ratio in optical microscopy/tomography. In addition, the intrinsic hemoglobin contrast PA neuroimaging has also been greatly improved by recent developments in nanoparticles (NPs). For instance, near-infrared absorbing NPs greatly enhanced the vascular contrast in deep-brain PAT; tumor-targeting NPs allowed highly sensitive and highly specific delineation of brain tumors; and multifunctional NPs enabled comprehensive examination of the brain through multimodal imaging. We aim to give an overview of NPs used in PA neuroimaging. Classifications of various NPs used in PAT will be introduced at the beginning, followed by an overview of PA neuroimaging systems, and finally we will discuss major applications of NPs in PA neuroimaging and highlight representative studies.



Photoacoustic (PA) tomography (PAT)1,2 is an emerging imaging modality that provides noninvasive high-resolution (20 to 100  μm) images of the entire brain in a preclinical setting at near real-time (temporal resolution <100  μs). PAT forms images by detecting the acoustic pressure induced by thermoelastic expansion following the absorption of optical energy, e.g., from laser light irradiation. Hence, the image contrast of PAT is primarily determined by the light absorption properties of the tissue, and the imaging frame rate is only limited by the laser’s pulse repetition rate (10 Hz to 5 kHz) and the speed of sound in tissue (typically 1.5  mm/μs). In brain tissues, the dominant endogenous optical absorber is hemoglobin, which enables label-free vascular imaging. Multispectrum PAT imaging allows the quantification of oxy- and deoxyhemoglobin (HbO2 and Hb) concentrations, which reveals oxygen saturation, an important physiological parameter that is difficult to measure with many other neuroimaging modalities. The broad choice of optical contrast agents, such as nanoparticles (NPs),3 chemical dyes, 4 and fluorescence proteins,5,6 further enhances the imaging capability of PAT, allowing for molecular brain imaging.

Compared with conventional contrast agents, NPs possess several unique advantages for PAT: (1) NPs’ optical absorption spectrum can be fine-tuned to meet specific imaging applications; (2) several targeting molecules can be integrated into one NP structure to enhance PAT specificity on identifying brain tumors; (3) some NPs’ rigid metallic structures are not susceptible to photobleaching, allowing for prolonged brain imaging; and (4) NPs’ large surface area or interior volume allows easy loading of imaging agents and drugs, enabling multimodal brain imaging and therapy. With these unique features, NPs are increasingly used in PA neuroimaging. This review aims to give an overview of developments in the field. Section 2 talks about the classification of NPs used in brain PAT. Section 3 reviews the five implementations of PA neuroimaging systems. Then, we discuss three major applications of NPs in PA neuroimaging and highlight representative studies. Finally, we conclude the review and discuss future directions. It should be noted that this review focuses only on NP-enabled PA neuroimaging. General reviews on PA neuroimaging or NPs used in PAT can be found in Refs. 78.9 and 1011.12, respectively.


Classification of Nanoparticles Used in Photoacoustic Brain Imaging

NPs, in general, refer to particles varying in diameter from 1 nanometer to several hundred nanometers. For biomedical imaging, most NPs have a size less than 100 nm to avoid rapid clearance from systemic circulation.13 At this dimension, particles exhibit unique optical properties from quantum effects and thus have a wide variety of applications in electronics, optics, and biomedicine.14,15 In this section, we give an overview of NPs that have been used in PAT in general and highlight the ones for PA neuroimaging. Our discussion will be based on the composition of NPs: organic NPs, inorganic NPs, and hybrid NPs.10

Organic NPs are formed with organic molecules that are bound together by chemical binding or self-assembly. Their good biocompatibility makes them appealing contrasts for in vivo imaging. Notable organic NPs used in PAT include porphysomes,16 perfluorocarbon-based (PFC) nanodroplets,17,18 polymer NPs,1920.21 hydrogel NPs,22 and perylene-3,4,9,10-tetracarboxylic diimide (PDI) NPs.23 Porphysomes have a liposome-like structure and are one of the first organic NPs designed to have strong near-infrared (NIR) absorption. They also exhibited excellent biocompatibility: even after a high-intravenous injection dose (1  g/kg mouse weight), mice still behaved normally, and a histopathological examination indicated good liver, spleen, and kidney functions. PFC nanodroplets were originally developed for ultrasound imaging. PA contrast can be introduced by loading nanodroplets with light absorbing materials. For instance, in indocyanine-green-loaded PFC nanodroplets, the PA contrast originated from indocyanine green (ICG), which is a food and drug administration approved contrast that absorbs around 800 nm.17 The intense optical absorption also makes the nanodroplets vaporize, which subsequently enhances the ultrasound contrast.2425.26.27 Among various polymer NPs, semiconducting polymers nanoparticles such as those made from poly (cyclopentadithiophene-alt-benzothiadiazole) are distinguished by their strong per-mass PA contrast and narrow absorption spectrum. In addition, they are resistant to photodegradation and oxidation, enabling in vivo imaging of reactive oxygen species, which is an important chemical mediator for many diseases.28 Hydrogel NPs are made of polyacrylamide (PAA) matrices with covalently linked Coomassie blue (CB) dye molecules.22 They are biocompatible, chemically inert, and nontoxic, and are the first type of organic NPs used in PA neuroimaging. However, their absorption in the visible region precludes in vivo deep-brain imaging. PDI is a class of small molecules that have exceptional chemical and photochemical stabilities and are extremely inexpensive. Their small molecule size and strong NIR absorption allow the imaging of deep brain tumors in live mice. Compared with inorganic NPs, organic PAT NPs have a relatively short development history and thus have only been used in limited PA neuroimaging studies.

Inorganic NPs used in PA include metallic NPs,29 quantum dots (QDs),30,31 iron oxide NPs,32,33 carbon nanotubes, 3435.36.37 and upconversion NPs.38 Gold NPs are the most popular group of metallic NPs used in PAT and PA neuroimaging, owing to their stable structure and strong extinction peak in the visible and NIR regions.39 By manipulating the size, shape, and internal structure, a variety of gold NPs, such as gold nanocages,39 gold nanoshells,40 and nanospheres,41 have been developed with different optical and loading capabilities. As will be discussed in the 3, gold NPs have been used in PA neuroimaging to enhance the vascular and tumor contrast. QDs are nanocrystals with sizes ranging from 2 to 10 nm.42 Their small size enhances transmigration across the blood brain barrier (BBB),43 which protects the brain from harmful substances but also prevents the effective delivery of therapeutic agents. QDs have excellent photostability, a large absorption cross section, and a high-quantum yield. They have been used in multimodal fluorescence, PA, and photothermal (PT) imaging.44 Iron oxide NPs were originally developed as magnetic resonance imaging (MRI) contrast agents.45 Bare iron oxide NPs have poor absorption in NIR and are thus not suitable for deep brain imaging. Silica coating has been proposed to enhance their NIR absorption.46 Carbon nanotubes are characterized by their small diameter (1 to 2 nm) and high aspect ratio (50 to 300 nm in length), which mitigates their clearance by the reticuloendothelial system.34 Similar to other NPs, carbon nanotubes have been used to enhance the tumor contrast in PAT. Upconversion NPs convert NIR absorption into emission in the visible region. However, their recent application in PAT was based on the luminescence quenching effect.38 In general, while they are less biocompatible, inorganic NPs have better optical tunability and are more stable than organic NPs. However, some inorganic NPs, such as iron oxide, have already been used to image human brains, and thus hold great promise for clinical PA neuroimaging.47

There is an another class of NPs called hybrid NPs, consisting of both inorganic and organic NP components. For instance, a gold-nanorod-encapsulated PFC nanodroplet contains inorganic gold nanorods for PAT and organic PFC for ultrasound imaging.48 The gold nanorods have better photostability than ICG, which was used in Ref. 17. While hybrid NPs holds the benefits of both organic and inorganic NPs, modification to the original organic/inorganic NP structure requires further investigation of its bio and photostabilities.


Photoacoustic Tomography Neuroimaging Systems

For better understanding of imaging experiments, this section gives a brief overview of PA neuroimaging systems. More comprehensive reviews of PAT systems can be found in Refs. 1, 2, 49, and 50. There are two major implementations of PA neuroimaging systems, one is based on photoacoustic microscopy (PAM) and the other is based on photoacoustic computed tomography (PACT). PAM is designed for high-resolution (1 to 50  μm) imaging over a shallow depth, while PACT targets at deeper imaging depth with compromised spatial resolution (50 to 200  μm).


Photoacoustic Microscopy Systems

According to the imaging depth and the spatial resolution, PAM can be classified into two groups: optical-resolution PAM (OR-PAM) and acoustic-resolution (AR-PAM) (as shown in Fig. 1). In OR-PAM, the lateral resolution is defined by the optical focus, which ranges from submicrometer to a few micrometers. Because OR-PAM relies on ballistic and/or quasiballistic photons, the imaging depth is less than one transport mean free path (TMFP, typically <1  mm in the brain). This depth is sufficient to cover the mouse cortex in an open scalp experiment. AR-PAM relies on diffusive light to form an image and its lateral resolution is defined by the acoustic focus. The imaging depth of AR-PAM is mainly determined by the penetration depth of the excitation wavelength and may vary from 1 mm (blue to green light) to a few mm (red to NIR light). AR-PAM can image the mouse brain cortex through an intact scalp. For both OR-PAM and AR-PAM, the axial resolution is defined by the bandwidth and central frequency of the ultrasound transducer. OR-PAM systems typically use higher central frequency transducers (50  MHz), which provide better axial resolutions. Image reconstruction in PAM systems is relatively simple because the spherically focused transducer mainly captures signals along the acoustic axis. Therefore, the PAM system forms an A-line of data at each scanning position. Combining all A-lines from two-dimensional (2-D) raster scan forms a three-dimensional (3-D) image.

Fig. 1

Schematics of (a) optical-resolution photoacoustic microscopy and (b) acoustic-resolution photoacoustic microscopy.


While PAM systems play an essential role in high-resolution functional brain imaging,5152.53 they were rarely used in NP studies, probably because (1) the shallow imaging depth does not need highly NIR absorbing NPs, and (2) the raster-scan requires high pulse repetition rate (>1  kHz) lasers, which typically lacks the wavelength tunability. Array-based PAM systems have recently been developed and may enable low-repetition rate lasers to be used in PAM.5455.56


Photoacoustic Computed Tomography Systems

Both PACT and AR-PAM rely on diffusive photons to generate PA signals. However, transducers used in PACT are unfocused toward the imaging plane and thus require computed tomography algorithms to form an image. For systems with matching numbers of data acquisition channels and array elements, a 2-D or 3-D image can be generated from a single laser shot.57 Most PACT systems use high-power Nd:YAG lasers, operating at 10 or 20 Hz. Wavelength tunability can be achieved through an optical parametric oscillator (OPO), a dye laser, or a Ti-sapphire laser. Based on the detection geometry, PACT can be divided into five categories: cylindrical-view PACT,58 planar-view PACT,59 spherical-view PACT,60 linear-view PACT,23 and circular-view PACT 61 (Fig. 2). For the first three geometries, unfocused transducer elements are evenly, or semievenly, distributed on the scanning surface, and 3-D images can be formed with near-isotropic spatial resolution. Due to the complete 3-D coverage, exact analytical image reconstruction algorithms, such as the universal back-projection algorithm, can be used in these 3-D geometries.62 The latter two geometries have a 2-D detection coverage and exact image reconstruction is still challenging.63,64 In practice, because linear and circular arrays are cylindrically focused on the 2-D detection plane, most researchers simply use the 3-D-based reconstruction algorithm in their 2-D systems. While the reconstruction may not be quantitatively accurate, the approximation is adequate for recovering dynamic changes in the brain or for extracting strong NP absorption from the hemoglobin background. 3-D PACT systems are commonly used in volumetric neuroimaging,60 while 2-D PACT systems are typically used for coronal- (linear-view PACT) or transverse-view (circular-view PACT) neuroimaging. It should be noted that 2-D PACT systems can also generate 3-D images by scanning vertically along the imaging plane. However, the spatial resolution along the third dimension will be poorer than their inplane resolutions.65 Advanced reconstruction algorithms or scanning geometries are needed to resolve this issue.65,66

Fig. 2

Schematics of: (a) cylindrical-view photoacoustic computed tomography (PACT), (b) planar-view PACT, (c) spherical-view PACT, (d) linear-view PACT, and (d) circular-view PACT.



Applications of Nanoparticles in Photoacoustic Neuroimaging


Contrast Enhancement

As previously mentioned, hemoglobin is the major intrinsic PA contrast, which enables label-free functional 67,68 and vascular brain imaging.9 However, in the NIR region, the optical absorption of hemoglobin is relatively weak, and contrasts from deep brain vessels are impeded by the surrounding tissue. NPs have been used to address these limitations because their absorption peaks can be systematically varied from visible to the NIR region. Among various types of NPs, gold NPs have been extensively used for PA contrast enhancement due to their strong NIR absorption, good biocompatibility, and durable structure. So far, four types of gold NPs have been used in PAT. They are nanoshells, nanocages, hollow nanospheres, and nanostars. Gold nanoshells are inorganic, optically tunable NPs consisting of a dielectric core (silica) surrounded by a thin-metallic layer (gold). Their optical resonance can vary precisely over a wide spectral range by adjusting the core size and thickness of the gold shell.40 Nanocages and hollow nanospheres are both hollow nanostructures, which exhibit improved surface plasmon resonance absorption over core-shell structures.69 Gold nanocages can be created through the reaction of Ag nanocubes and HAuCl4, and their name originates from the hollow and porous structures.70 Hollow gold nanospheres have a highly uniform structure and exhibit similar optical absorption properties as nanocages.69,71 Gold nanostars contain multiple sharp tips, which create a “lightning rod” effect to further enhance the local surface plasmon effort.72

For in vivo imaging, gold NPs are commonly coated with polyethylene glycol (PEG) to suppress the immunogenic response and subsequently improve the biostability.73 The feasibility of using PEG-coated nanoshells to enhance PAT was first demonstrated by Wang et al.40 in rat brain imaging. The nanoshells used in the experiment had a 10 to 12-nm thick gold shell with peak absorption at 800±5  nm. The experiment was performed on a circular-view PACT system with a 2-mm-diameter nonfocused ultrasonic transducer scanning around the rat’s head. A tunable dye laser with an 800-nm emission and a 10-Hz pulse repetition rate was used as the excitation source. Due to the slow mechanical scanning, acquiring each slice took 24 min. After three sequential nanoshells injections through the tail vein, the absorption of blood was increased by 63% [Figs. 3(a) and 3(b)]. Similar setups have also been used to image contrast enhancements from gold nanocages 74 and hollow gold nanospheres.41

Fig. 3

Noninvasive photoacoustic (PA) neuroimaging employing gold nanoparticles (NPs). (a) and (d) PA images acquired through an intact rat scalp before and 20 min after tail vein injection of gold nanoshells, respectively. The experiment was performed on a single-element–based circular-view PACT system. (c) PA image acquired through an intact mouse scalp after nanostar injection. R: rostral rhinal vein. S: sagittal sinus. T: transverse sinus. (d) PA intensity (normalized to the first frame) of sagittal sinus calculated from each frame. Inset, normalized PA intensity monitored for the initial 600 s. The experiment was performed on an array-based circular-view PACT system. Reproduced with permission from Refs. 40 and 72.


Recently, an array-based circular-view PACT system has been used to image contrast enhancement from gold nanostars [Figs. 3(c) and 3(d)].72 The system had 512 transducer elements evenly distributed on a 5-cm diameter circle. Each element was arc-shaped with a 1.9-cm radius of curvature along elevation direction. This design ensured rejection of out-of-plane signals.75 The array system eliminates mechanical scanning and thus significantly improves the imaging speed—a 2-D image can be captured in 0.625 s. To match the absorption peak of nanostars, a Ti-Sapphire laser with 800-nm output was used as the excitation source. The maximum light intensity on mouse scalp was approximately 15  mJ/cm2, which is below the American National Standard Institute (ANSI) safety limit of 30  mJ/cm. The high imaging speed allows for monitoring of dynamic changes in PA amplitude. As can be seen in Fig. 3(d), the PA amplitude rose almost instantly after tail vein injection of nanostars and then it increased gradually before reaching the maximum at around half an hour. The PA signal then gradually decreased, indicating the clearance of nanostars the reticuloendothelial system (RES).


Tumor Targeting

In addition to vascular contrast enhancement, NPs have also been used in tumor targeting.76,77 The targeting mechanism can be either passive or active. Passive targeting is based on the enhanced permeability and retention effect (EPR effect),78,79 which allows NPs to accumulate at a higher concentration in tumors than in healthy tissues.80 The EPR effect relies on two mechanisms: first, the porous vascular structures in tumors facilitate the perfusion of NPs; second, once NPs are in a tumor, they tend to stay for a prolonged period of time because of poor lymphatic drainage in the tumor, leading to a higher NP concentration.

Passive brain tumor targeting was recently demonstrated in PA neuroimaging using organic PDI NPs.23 In this study, PDI NPs had an average size of 50 nm and exhibited strong absorption at 700 nm, which enabled deep-brain tumor imaging. The experiment was performed using a commercial linear-view PACT system (Vevo LARZ, Visualsonics) with a LZ-250 linear array (13–24 MHz central frequency) and a tunable OPO laser system (680–970 nm) with a 20 Hz pulse repetition rate. When all 256 elements were used for imaging, the LARZ system had a frame rate of 5 Hz. The experiment was performed on mice with orthotopic glioblastoma tumors. Before the PA experiment, the authors first scanned the mouse with an MRI to confirm tumor size and location. They then injected 250  μL of 250 nM PDI NPs through the tail vein and imaged the animal with the LARZ system at 0 hour, 2 hours, 1 day, and 2 days post injection. Figure 4 shows coronal-view images of the mouse brain. The red dashed line indicates the skull, while the blue dashed circle indicates the tumor region. An obvious increase of PA amplitude at the tumor site can be observed starting from day 1. The depth of the tumor was estimated to be 4 mm, which agreed with the MRI image. The tumor contrast continued to increase in day 2, indicating enhanced tumor penetration of NPs with time, while the skull contrast started to decrease, indicating the clearance of NPs in the circulatory system.23

Fig. 4

Coronal-view PA images demonstrating the effect of passive tumor targeting with PDI NPs. Images were acquired after tail vein injection of 250  μL of 250 nM PDI NPs in a mouse with an orthotopic glioblastoma tumor. Adapted with permission from Ref. 23.


Despite encouraging results, passive targeting has its inherent limitations. The cells of RES will remove most of the intravascular injected NPs,81 and the spleen, liver, lung, bone marrow, and kidney would also uptake NPs. Thus, only a small fraction of administered NPs can reach the tumor.82,83 To increase the circulation time, the size of the NPs needs to be less than 100 nm, and the surface biocompatibility needs to be carefully designed.

Another targeting mechanism is active targeting, which uses the receptors that are highly expressed on the surface of tumor cells, such as the epidermal growth factor receptors (EGFR) and integrin.84 When NPs are decorated with ligands that can specifically bind to these receptors, the concentration of NPs in the tumor will increase. Because of the large surface area of NPs, many ligands, such as proteins and peptides, can be coated on NPs.85 Active targeting complements passive targeting with the EPR effect to provide prolonged and even targeted accumulation of NPs in tumors.

A preliminary demonstration of activate tumor targeting was carried out using organic Blue NPs, which were made of a PAA matrix with covalently linked CB dye molecules and were conjugated with F3 peptide.22 The F3 peptide binds to tumor endothelial cells while the CB dye enhances optical absorption at 590 nm. The study was performed on rats with 9L glioma tumors in their brains. Animals were euthanized several days after a tail vein injection of NPs to avoid untargeted accumulation. Subsequently, the brains were excised for ex vivo PAT. The experiment was performed on a circular-view PACT system with a single, cylindrically focused 9 MHz transducer. A dye laser (ND6000, Continuum) with a 10 Hz pulse repetition rate and an output at 590 nm (the absorption peak for NPs) was used as the excitation source. The incident light intensity was 3  mJ/cm2, which was well below the American National Standard Institute limit of 20  mJ/cm2. Because of NPs’ strong optical absorption and targeting properties, the brain tumor could be clearly delineated in the PA image [Fig. 5(a)], even when the dose of NPs (125  mg/kg of rat mass) was at a level indistinguishable by the naked eye in the photograph [Fig. 5(b)]. This study demonstrates the potential of intraoperative tumor delineation using PAT.

Fig. 5

(a) PA image of an excised rat brain containing a tumor treated with nanoshells. Field of view: 2  cm×2  cm. (b) Photograph of the brain in (a). Adapted with permission from Ref. 22.



Multimodal Imaging

Multimodal imaging allows for a more comprehensive characterization of a brain in its healthy and diseased states.86 NPs are one of the most attractive multimodal contrast agents because their multicomponent nature offers many possibilities to incorporate various imaging probes. Because the same NPs can be visualized in different imaging modalities, they allow precise coregistration of multimodal images and corresponding tissue information.

A notable multimodal probe used in PA neuroimaging is trimodal MRI-PAT-Raman imaging (MPR) NPs.87 MPR NPs consisted of a 60-nm gold core covered with a Raman active layer, which was further coated with silica and Gd3+, resulting in a gold-silica–based NP with both Raman and magnetic contrasts. MPR NP performances were measured on glioblastoma-bearing mice with contrasts injected through the tail vein. Imaging experiments were performed several hours after injection to let MPR NPs gradually accumulate in the tumors through the passive EPR effect. PA images were acquired by an AR-PAM system. However, unlike typical AR-PAM systems with kHz repetition rate lasers, their system employed a 10-Hz Nd:YAG pulsed laser (Nd:YAG laser), whose 532-nm output was coupled into a ring fiber optical bundle. A 5-MHz focused transducer was placed at the center of the fiber bundle for signal acquisition. The spatial resolution of the system was 0.6 and 0.38 mm along lateral and axial resolutions, respectively. Figure 6 indicates that MPR NPs can be clearly visualized in all three modalities. The MRI anatomical image allows for the precise localization of tumor position, PAT provides high-resolution 3-D images of the tumor, and Raman enables surface imaging of tumor margins with high sensitivity and high specificity.87

Fig. 6

MPR multimodal images of a mouse brain. (a) Magnetic resonance imaging (MRI) image, (b) PA image (green) superimposed on MRI image, and (c) Raman (red) superimposed on MRI image. Reproduced with permission from Ref. 87.


There are many other multimodal NPs that show great potential for PA neuroimaging. For instance, because of strong optical absorption, most NPs also allow PT tumor therapy and PAT.88,89 PAT provides high-resolution images of NP distribution and tumor vasculature and offers real-time monitoring of temperature rise during PT therapy.72,90 Single-walled carbon nanotubes have enabled multimodal thermoacoustic tomography and PAT, due to their intrinsic absorption at both optical and radio frequencies.91 QDs have been used in multimodal PAT and fluorescence imaging, due to their broad excitation spectra (400 to 700 nm) and narrow emission spectra (30 to 80 nm).44



Because of their unique properties and advantages, NPs have been increasingly used in PA neuroimaging. This review provided an overview of NPs used in PAT and highlighted their applications in PA neuroimaging. However, PAT NPs only cover a very small variety of all NPs that have been developed so far. The major impediment is that many NPs, such as the clinically approved iron oxide NPs, do not exhibit strong absorption in the red or NIR region, which is essential for deep-brain PAT. Modification of surface coating or encapsulating with light absorption materials is needed to improve the PA contrast of those NPs. There are also many other exciting applications that have not been demonstrated in PA neuroimaging. For instance, because the plasmonic resonance frequencies depend on the dielectric properties of the media, metallic NPs can potentially be used to sense electrostatic fields induced by neural firing.92 This would offer a significant advantage over dye-based action potential imaging because most voltage-sensitive dyes operate in the visible region.93 NPs have also been used to measure brain glucose levels, which provide insight on cerebral metabolism.94 This technique can potentially replace brain fludeoxyglucose positron emission tomography, which contains ionizing radiation. PA guidance of brain therapy using NPs loaded with drugs is also a very promising application.95 Therapeutic drugs can be encapsulated in an NP to be delivered and attached to the brain tumor site. Upon external excitation, the drug can be released on site, minimizing damage to healthy brain tissue. PAT can be used to monitor the process of drug release and provide real-time feedback on tissue function.

However, while preclinical imaging results are encouraging, there is still a long way to go before NPs can be used for clinical PA neuroimaging. On the NP side, the BBB crossing efficiency and biosafety need further investigation. For studies discussed in Sec. 4.2,23 NPs reached the brain tumor based on diffusion through disrupted BBB (due to the presence of tumor). However, the passive diffusion has a very low-crossing efficiency and only works on certain brain disorders, such as the traumatic brain injury and malignant brain tumors. Recent progresses on receptor-mediated transcytosis have shown great promise to address this issue.96 They are based on the fact that brain cells require a constant supply of nutrition, e.g., iron and glucose, to maintain their function. These nutrients and carrier proteins are able to bind with receptors expressed on brain endothelial cells and cross the BBB through receptor-mediated transcytosis. When NPs are coated with certain molecules, such as transferrin and insulin, they can be coupled to the corresponding receptors on the brain endothelial cells and be escorted through BBB. Alternatively, instead of systemic delivery through the tail vein, transnasal delivery can be used on lipid-soluble small molecules to bypass the BBB.97 As for biosafety, there is still little information on the potential toxicity of NPs to human health. As can be seen from Sec. 2, NPs can be composited from a wide variety of materials, whose bioeffects may greatly vary. PEG coating is a common approach to prevent potential toxicity of NPs.98 However, PEG-coated NPs may still be trapped in the liver and spleen for a prolonged period and their long-term effect is still unclear. BBB-penetrating NPs may also affect the central nervous system. Their neurotoxicity is also a very poorly understood area.99

On the PA side, several technical improvements are also needed. Current PAT systems are relatively bulky and can only operate on an optical table to image anesthetized animals. There is a need for a miniaturized PAT system that can be mounted on the animal head to image freely moving animals (similar to the widely used Inscopix cameras). This may open a new avenue for monitoring behavior-related neuro and hemodynamic activities using PAT. Recently, a promising progress in this direction was reported.21 Another emerging need for PAT is to minimize the acoustic distortion from skull. Even for mice imaging, the skull and bone cavities may severely degrade deep brain imaging quality. To address this issue, the bone profile needs to be mapped through another modality, such as x-ray computed tomography or ultrasound computed tomography, and be incorporated into PAT reconstruction.100

Nevertheless, with increasing effort in NP research and PA imaging, great progresses have been shown to overcome the aforementioned limitations.101102.103 In the next few years, we expect to see a wider adoption of NPs in PA neuroimaging to improve our understanding of the brain and to advance the treatment of brain diseases.


This work was sponsored by University at Buffalo’s Start Up fund.


1. L. V. Wang and S. Hu, “Photoacoustic tomography: in vivo imaging from organelles to organs,” Science 335(6075), 1458–1462 (2012).SCIEAS0036-8075 http://dx.doi.org/10.1126/science.1216210 Google Scholar

2. M. Xu and L. V. Wang, “Photoacoustic imaging in biomedicine,” Rev. Sci. Instrum. 77(4), 041101 (2006).RSINAK0034-6748 http://dx.doi.org/10.1063/1.2195024 Google Scholar

3. H. Xu et al., “Nanoscale optical probes for cellular imaging,” Chem. Soc. Rev. 43(8), 2650–2661 (2014).CSRVBR0306-0012 http://dx.doi.org/10.1039/c3cs60309a Google Scholar

4. X. Wang et al., “Noninvasive photoacoustic angiography of animal brains in vivo with near-infrared light and an optical contrast agent,” Opt. Lett. 29(7), 730–732 (2004).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.29.000730 Google Scholar

5. D. Razansky et al., “Multispectral opto-acoustic tomography of deep-seated fluorescent proteins in vivo,” Nat. Photonics 3(7), 412–417 (2009).NPAHBY1749-4885 http://dx.doi.org/10.1038/nphoton.2009.98 Google Scholar

6. G. S. Filonov et al., “Deep-tissue photoacoustic tomography of a genetically encoded near-infrared fluorescent probe,” Angew. Chem. 124(6), 1477–1480 (2012).ANCEAD0044-8249 http://dx.doi.org/10.1002/ange.201107026 Google Scholar

7. J. Yao and L. V. Wang, “Photoacoustic brain imaging: from microscopic to macroscopic scales,” Neurophotonics 1(1), 011003 (2014). http://dx.doi.org/10.1117/1.NPh.1.1.011003 Google Scholar

8. J. Xia and L. V. Wang, “Photoacoustic tomography of the brain,” in Optical Methods and Instrumentation in Brain Imaging and Therapy, pp. 137–156, Springer, New York (2013). Google Scholar

9. S. Hu and L. V. Wang, “Neurovascular photoacoustic tomography,” Front. Neuroenerg. 3, 1–7 (2010). http://dx.doi.org/10.3389/fnene.2010.00010 Google Scholar

10. H. Chen, Z. Yuan and C. Wu, “Nanoparticle probes for structural and functional photoacoustic molecular tomography,” BioMed Res. Int. 2015, 1–11 (2015). http://dx.doi.org/10.1155/2015/757101 Google Scholar

11. C. Kim, C. Favazza and L. V. Wang, “In vivo photoacoustic tomography of chemicals: high-resolution functional and molecular optical imaging at new depths,” Chem. Rev. 110(5), 2756–2782 (2010).CHREAY0009-2665 http://dx.doi.org/10.1021/cr900266s Google Scholar

12. L. Nie and X. Chen, “Structural and functional photoacoustic molecular tomography aided by emerging contrast agents,” Chem. Soc. Rev. 43(20), 7132–7170 (2014).CSRVBR0306-0012 http://dx.doi.org/10.1039/C4CS00086B Google Scholar

13. F. Alexis et al., “Factors affecting the clearance and biodistribution of polymeric nanoparticles,” Mol. Pharm. 5(4), 505–515 (2008).MPOHBP1543-8384 http://dx.doi.org/10.1021/mp800051m Google Scholar

14. J. L. West and N. J. Halas, “Engineered nanomaterials for biophotonics applications: improving sensing, imaging, and therapeutics,” Annu. Rev. Biomed. Eng. 5(1), 285–292 (2003).ARBEF71523-9829 http://dx.doi.org/10.1146/annurev.bioeng.5.011303.120723 Google Scholar

15. M. Holzinger, A. Le Goff and S. Cosnier, “Nanomaterials for biosensing applications: a review,” Front. Chem. 3, 1–10 (2014). http://dx.doi.org/10.3389/fchem.2014.00063 Google Scholar

16. J. F. Lovell et al., “Porphysome nanovesicles generated by porphyrin bilayers for use as multimodal biophotonic contrast agents,” Nat. Mater. 10(4), 324–332 (2011).NMAACR1476-1122 http://dx.doi.org/10.1038/nmat2986 Google Scholar

17. A. Hannah et al., “Indocyanine green-loaded photoacoustic nanodroplets: dual contrast nanoconstructs for enhanced photoacoustic and ultrasound imaging,” ACS Nano 8(1), 250–259 (2013).ANCAC31936-0851 http://dx.doi.org/10.1021/nn403527r Google Scholar

18. W. J. Akers et al., “Noninvasive photoacoustic and fluorescence sentinel lymph node identification using dye-loaded perfluorocarbon nanoparticles,” ACS Nano 5(1), 173–182 (2010).ANCAC31936-0851 http://dx.doi.org/10.1021/nn102274q Google Scholar

19. Y. Li et al., “A dual-targeting nanocarrier based on poly (amidoamine) dendrimers conjugated with transferrin and tamoxifen for treating brain gliomas,” Biomaterials 33(15), 3899–3908 (2012).BIMADU0142-9612 http://dx.doi.org/10.1016/j.biomaterials.2012.02.004 Google Scholar

20. H. Xin et al., “Anti-glioblastoma efficacy and safety of paclitaxel-loading Angiopep-conjugated dual targeting PEG-PCL nanoparticles,” Biomaterials 33(32), 8167–8176 (2012).BIMADU0142-9612 http://dx.doi.org/10.1016/j.biomaterials.2012.07.046 Google Scholar

21. J. Tang et al., “Noninvasive high-speed photoacoustic tomography of cerebral hemodynamics in awake-moving rats,” J. Cerebral Blood Flow Metab. 35(8), 1224–1232 (2015). http://dx.doi.org/10.1038/jcbfm.2015.138 Google Scholar

22. A. Ray et al., “Targeted blue nanoparticles as photoacoustic contrast agent for brain tumor delineation,” Nano Res. 4(11), 1163–1173 (2011).1998-0124 http://dx.doi.org/10.1007/s12274-011-0166-1 Google Scholar

23. Q. Fan et al., “Perylene-diimide-based nanoparticles as highly efficient photoacoustic agents for deep brain tumor imaging in living mice,” Adv. Mater. 27(5), 843–847 (2015).ADVMEW0935-9648 http://dx.doi.org/10.1002/adma.201402972 Google Scholar

24. O. D. Kripfgans et al., “Acoustic droplet vaporization for therapeutic and diagnostic applications,” Ultrasound Med. Biol. 26(7), 1177–1189 (2000). http://dx.doi.org/10.1016/S0301-5629(00)00262-3 Google Scholar

25. T. Giesecke and K. Hynynen, “Ultrasound-mediated cavitation thresholds of liquid perfluorocarbon droplets in vitro,” Ultrasound Med. Biol. 29(9), 1359–1365 (2003). http://dx.doi.org/10.1016/S0301-5629(03)00980-3 Google Scholar

26. P. S. Sheeran and P. A. Dayton, “Phase-change contrast agents for imaging and therapy,” Curr. Pharm. Des. 18(15), 2152–2165 (2012). http://dx.doi.org/10.2174/138161212800099883 Google Scholar

27. N. Reznik et al., “Optical studies of vaporization and stability of fluorescently labelled perfluorocarbon droplets,” Phys. Med. Biol. 57(21), 7205 (2012).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/57/21/7205 Google Scholar

28. K. Pu et al., “Semiconducting polymer nanoparticles as photoacoustic molecular imaging probes in living mice,” Nat. Nanotechnol. 9(3), 233–239 (2014).NNAABX1748-3387 http://dx.doi.org/10.1038/nnano.2013.302 Google Scholar

29. J. Chen et al., “Gold nanocages: bioconjugation and their potential use as optical imaging contrast agents,” Nano Lett. 5(3), 473–477 (2005).NALEFD1530-6984 http://dx.doi.org/10.1021/nl047950t Google Scholar

30. W. C. W. Chan et al., “Luminescent quantum dots for multiplexed biological detection and imaging,” Curr. Opin. Biotechnol. 13(1), 40–46 (2002).CUOBE30958-1669 http://dx.doi.org/10.1016/S0958-1669(02)00282-3 Google Scholar

31. X. Gao et al., “In vivo molecular and cellular imaging with quantum dots,” Curr. Opin. Biotechnol. 16(1), 63–72 (2005).CUOBE30958-1669 http://dx.doi.org/10.1016/j.copbio.2004.11.003 Google Scholar

32. X. Feng, F. Gao and Y. Zheng, “Thermally modulated photoacoustic imaging with super-paramagnetic iron oxide nanoparticles,” Opt. Lett. 39(12), 3414–3417 (2014).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.39.003414 Google Scholar

33. Y. Jin et al., “Multifunctional nanoparticles as coupled contrast agents,” Nat. Commun. 1, 41 (2010).NCAOBW2041-1723 http://dx.doi.org/10.1038/ncomms1042 Google Scholar

34. A. De La Zerda et al., “Carbon nanotubes as photoacoustic molecular imaging agents in living mice,” Nat. Nanotechnol. 3(9), 557–562 (2008).NNAABX1748-3387 http://dx.doi.org/10.1038/nnano.2008.231 Google Scholar

35. S. Zanganeh et al., “Photoacoustic imaging enhanced by indocyanine green-conjugated single-wall carbon nanotubes,” J. Biomed. Opt. 18(9), 096006 (2013).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.18.9.096006 Google Scholar

36. P. K. Avti et al., “Detection, mapping, and quantification of single walled carbon nanotubes in histological specimens with photoacoustic microscopy,” PLoS One 7(4), e35064 (2012).POLNCL1932-6203 http://dx.doi.org/10.1371/journal.pone.0035064 Google Scholar

37. V. P. Nguyen et al., “Enhancement of high-resolution photoacoustic imaging with indocyanine green-conjugated carbon nanotubes,” Jpn. J. Appl. Phys. 54(7S1), 07HF04 (2015).JJAPA50021-4922 http://dx.doi.org/10.7567/JJAP.54.07HF04 Google Scholar

38. S. K. Maji et al., “Upconversion nanoparticles as a contrast agent for photoacoustic imaging in live mice,” Adv. Mater. 26(32), 5633–5638 (2014).ADVMEW0935-9648 http://dx.doi.org/10.1002/adma.201400831 Google Scholar

39. J. Chen et al., “Gold nanocages: engineering their structure for biomedical applications,” Adv. Mater. 17(18), 2255–2261 (2005).ADVMEW0935-9648 http://dx.doi.org/10.1002/adma.200500833 Google Scholar

40. Y. Wang et al., “Photoacoustic tomography of a nanoshell contrast agent in the in vivo rat brain,” Nano Lett. 4(9), 1689–1692 (2004).NALEFD1530-6984 http://dx.doi.org/10.1021/nl049126a Google Scholar

41. W. Lu et al., “Photoacoustic imaging of living mouse brain vasculature using hollow gold nanospheres,” Biomaterials 31(9), 2617–2626 (2010).BIMADU0142-9612 http://dx.doi.org/10.1016/j.biomaterials.2009.12.007 Google Scholar

42. G. Xu et al., “Theranostic quantum dots for crossing blood-brain barrier in vitro and providing therapy of HIV-associated encephalopathy,” Front. Pharmacol. 4, 1–8 (2013). http://dx.doi.org/10.3389/fphar.2013.00140 Google Scholar

43. S. Hanada et al., “Cell-based in vitro blood-brain barrier model can rapidly evaluate nanoparticles’ brain permeability in association with particle size and surface modification,” Int. J. Mol. Sci. 15(2), 1812–1825 (2014).1422-0067 http://dx.doi.org/10.3390/ijms15021812 Google Scholar

44. E. V. Shashkov et al., “Quantum dots as multimodal photoacoustic and photothermal contrast agents,” Nano Lett. 8(11), 3953–3958 (2008).NALEFD1530-6984 http://dx.doi.org/10.1021/nl802442x Google Scholar

45. R. Weissleder et al., “Experimental lymph node metastases: enhanced detection with MR lymphography,” Radiology 171(3), 835–839 (1989).RADLAX0033-8419 http://dx.doi.org/10.1148/radiology.171.3.2717761 Google Scholar

46. R. Alwi et al., “Silica-coated super paramagnetic iron oxide nanoparticles (SPION) as biocompatible contrast agent in biomedical photoacoustics,” Biomed. Opt. Express 3(10), 2500–2509 (2012).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.3.002500 Google Scholar

47. W. S. Enochs et al., “Improved delineation of human brain tumors on MR images using a long-circulating, superparamagnetic iron oxide agent,” J. Magn. Reson. Imaging 9(2), 228–232 (1999). http://dx.doi.org/10.1002/(SICI)1522-2586(199902)9:2<228::AID-JMRI12>3.0.CO;2-K Google Scholar

48. A. S. Hannah et al., “Photoacoustic and ultrasound imaging using dual contrast perfluorocarbon nanodroplets triggered by laser pulses at 1064 nm,” Biomed. Opt. Express 5(9), 3042–3052 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.003042 Google Scholar

49. L. V. Wang, “Ultrasound-mediated biophotonic imaging: a review of acousto-optical tomography and photo-acoustic tomography,” Disease Markers 19(2–3), 123–138 (2004).DMARD30278-0240 http://dx.doi.org/10.1155/2004/478079 Google Scholar

50. J. Xia and L. V. Wang, “Small-animal whole-body photoacoustic tomography: a review,” IEEE Trans. Biomed. Eng. 61(5), 1380–1389 (2014). http://dx.doi.org/10.1109/TBME.2013.2283507 Google Scholar

51. J. Yao et al., “High-speed label-free functional photoacoustic microscopy of mouse brain in action,” Nat. Methods 12(5), 407–410 (2015).1548-7091 http://dx.doi.org/10.1038/nmeth.3336 Google Scholar

52. L. Wang, K. Maslov and L. V. Wang, “Single-cell label-free photoacoustic flowoxigraphy in vivo,” Proc. Natl. Acad. Sci. 110(15), 5759–5764 (2013). http://dx.doi.org/10.1073/pnas.1215578110 Google Scholar

53. X. Yang et al., “Photoacoustic tomography of small animal brain with a curved array transducer,” J. Biomed. Opt. 14(5), 054007 (2009). http://dx.doi.org/10.1117/1.3227035 Google Scholar

54. L. Song, K. Maslov and L. V. Wang, “Multifocal optical-resolution photoacoustic microscopy in vivo,” Opt. Lett. 36(7), 1236–1238 (2011).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.36.001236 Google Scholar

55. G. Li, K. I. Maslov and L. V. Wang, “Reflection-mode multifocal optical-resolution photoacoustic microscopy,” J. Biomed. Opt. 18(3), 030501 (2013).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.18.3.030501 Google Scholar

56. J. Xia et al., “Wide-field two-dimensional multifocal optical-resolution photoacoustic-computed microscopy,” Opt. Lett. 38(24), 5236–5239 (2013).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.38.005236 Google Scholar

57. S. Gottschalk et al., “Noninvasive real-time visualization of multiple cerebral hemodynamic parameters in whole mouse brains using five-dimensional optoacoustic tomography,” J. Cerebral Blood Flow Metab. 35(4), 531–535 (2015). http://dx.doi.org/10.1038/jcbfm.2014.249 Google Scholar

58. X. Wang et al., “Three-dimensional laser-induced photoacoustic tomography of mouse brain with the skin and skull intact,” Opt. Lett. 28(19), 1739–1741 (2003).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.28.001739 Google Scholar

59. J. Laufer et al., “Three-dimensional noninvasive imaging of the vasculature in the mouse brain using a high resolution photoacoustic scanner,” Appl. Opt. 48(10), D299–D306 (2009).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.48.00D299 Google Scholar

60. L. Xiang et al., “4-D photoacoustic tomography,” Sci. Rep. 3, 1–8 (2013). http://dx.doi.org/10.1038/srep01113 Google Scholar

61. Z. Guo, S. Hu and L. V. Wang, “Calibration-free absolute quantification of optical absorption coefficients using acoustic spectra in 3D photoacoustic microscopy of biological tissue,” Opt. Lett. 35(12), 2067–2069 (2010).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.35.002067 Google Scholar

62. M. Xu and L. V. Wang, “Universal back-projection algorithm for photoacoustic computed tomography,” Proc. SPIE 5697, 251–254 (2005).PSISDG0277-786X http://dx.doi.org/10.1117/12.589146 Google Scholar

63. D. Finch, M. Haltmeier and Rakesh, “Inversion of spherical means and the wave equation in even dimensions,” SIAM J. Appl. Math. 68(2), 392–412 (2007).SMJMAP0036-1399 http://dx.doi.org/10.1137/070682137 Google Scholar

64. K. Wang and M. A. Anastasio, “A simple Fourier transform-based reconstruction formula for photoacoustic computed tomography with a circular or spherical measurement geometry,” Phys. Med. Biol. 57(23), N493 (2012).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/57/23/N493 Google Scholar

65. J. Xia et al., “Three-dimensional photoacoustic tomography based on the focal-line concept,” J. Biomed. Opt. 16(9), 090505 (2011).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.3625576 Google Scholar

66. J. Gateau et al., “Single-side access, isotropic resolution, and multispectral three-dimensional photoacoustic imaging with rotate-translate scanning of ultrasonic detector array,” J. Biomed. Opt. 20(5), 056004 (2015).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.20.5.056004 Google Scholar

67. X. Wang et al., “Noninvasive laser-induced photoacoustic tomography for structural and functional in vivo imaging of the brain,” Nat. Biotechnol. 21(7), 803–806 (2003).NABIF91087-0156 http://dx.doi.org/10.1038/nbt839 Google Scholar

68. M. Nasiriavanaki et al., “High-resolution photoacoustic tomography of resting-state functional connectivity in the mouse brain,” Proc. Natl. Acad. Sci. 111(1), 21–26 (2014). http://dx.doi.org/10.1073/pnas.1311868111 Google Scholar

69. A. M. Schwartzberg et al., “Synthesis, characterization, and tunable optical properties of hollow gold nanospheres,” J. Phys. Chem. B 110(40), 19935–19944 (2006). http://dx.doi.org/10.1021/jp062136a Google Scholar

70. W. Li et al., “Gold nanocages as contrast agents for photoacoustic imaging,” Contrast Media Mol. Imaging 6(5), 370–377 (2011). http://dx.doi.org/10.1002/cmmi.439 Google Scholar

71. M. P. Melancon et al., “In vitro and in vivo targeting of hollow gold nanoshells directed at epidermal growth factor receptor for photothermal ablation therapy,” Mol. Cancer Ther. 7(6), 1730–1739 (2008). http://dx.doi.org/10.1158/1535-7163.MCT-08-0016 Google Scholar

72. H. Yuan et al., “Plasmonics-enhanced and optically modulated delivery of gold nanostars into brain tumor,” Nanoscale 6(8), 4078–4082 (2014).NANOHL2040-3364 http://dx.doi.org/10.1039/c3nr06770j Google Scholar

73. N. E. Martin and M. Modi, “Pegylation: a novel process for modifying pharmacokinetics,” Clin. Pharmacokinet. 40(7), 539–551 (2001). http://dx.doi.org/10.2165/00003088-200140070-00005 Google Scholar

74. X. Yang et al., “Photoacoustic tomography of a rat cerebral cortex in vivo with Au nanocages as an optical contrast agent,” Nano Lett. 7(12), 3798–3802 (2007).NALEFD1530-6984 http://dx.doi.org/10.1021/nl072349r Google Scholar

75. J. Gamelin et al., “A real-time photoacoustic tomography system for small animals,” Opt. Express 17(13), 10489–10498 (2009).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.17.010489 Google Scholar

76. G. Nie et al., “Hydrogel nanoparticles with covalently linked Coomassie blue for brain tumor delineation visible to the surgeon,” Small 8(6), 884–891 (2012).SMALBC1613-6810 http://dx.doi.org/10.1002/smll.201101607 Google Scholar

77. S. M. Moghimi, A. C. Hunter and J. C. Murray, “Long-circulating and target-specific nanoparticles: theory to practice,” Pharmacol. Rev. 53(2), 283–318 (2001).PAREAQ0031-6997 Google Scholar

78. H. Maeda et al., “Vascular permeability enhancement in solid tumor: various factors, mechanisms involved and its implications,” Int. Immunopharmacol. 3(3), 319–328 (2003). http://dx.doi.org/10.1016/S1567-5769(02)00271-0 Google Scholar

79. H. F. Dvorak et al., “Identification and characterization of the blood vessels of solid tumors that are leaky to circulating macromolecules,” Am. J. Pathol. 133(1), 95 (1988).AJPAA40002-9440 Google Scholar

80. Y. Matsumura and H. Maeda, “A new concept for macromolecular therapeutics in cancer chemotherapy: mechanism of tumoritropic accumulation of proteins and the antitumor agent smancs,” Cancer Res. 46(12 Part 1), 6387–6392 (1986).CNREA80008-5472 Google Scholar

81. M. A. Dobrovolskaia and S. E. McNeil, “Immunological properties of engineered nanomaterials,” Nat. Nanotechnol. 3(8), 469–478 (2007).NNAABX1748-3387 http://dx.doi.org/10.1038/nnano.2007.223 Google Scholar

82. N. Khlebtsov and L. Dykman, “Biodistribution and toxicity of engineered gold nanoparticles: a review of in vitro and in vivo studies,” Chem. Soc. Rev. 40(3), 1647–1671 (2011).CSRVBR0306-0012 http://dx.doi.org/10.1039/C0CS00018C Google Scholar

83. H. Yan et al., “Two-order targeted brain tumor imaging by using an optical/paramagnetic nanoprobe across the blood brain barrier,” ACS nano 6(1), 410–420 (2011).ANCAC31936-0851 http://dx.doi.org/10.1021/nn203749v Google Scholar

84. J. S. Desgrosellier and D. A. Cheresh, “Integrins in cancer: biological implications and therapeutic opportunities,” Nat. Rev. Cancer 10(1), 9–22 (2010).NRCAC41474-175X http://dx.doi.org/10.1038/nrc2748 Google Scholar

85. M. Qin, H. Zong and R. Kopelman, “Click conjugation of peptide to hydrogel nanoparticles for tumor-targeted drug delivery,” Biomacromolecules 15(10), 3728–3734 (2014).BOMAF61525-7797 http://dx.doi.org/10.1021/bm501028c Google Scholar

86. J. Mansik and K. Chulhong, “Multimodal photoacoustic tomography,” IEEE Trans. Multimedia 15(5), 975–982 (2013). http://dx.doi.org/10.1109/TMM.2013.2244203 Google Scholar

87. M. F. Kircher et al., “A brain tumor molecular imaging strategy using a new triple-modality MRI-photoacoustic-Raman nanoparticle,” Nat. Med. 18(5), 829–834 (2012).1078-8956 http://dx.doi.org/10.1038/nm.2721 Google Scholar

88. J. W. Kim et al., “Golden carbon nanotubes as multimodal photoacoustic and photothermal high-contrast molecular agents,” Nat. Nanotechnol. 4(10), 688–694 (2009).NNAABX1748-3387 http://dx.doi.org/10.1038/nnano.2009.231 Google Scholar

89. H. W. Yang et al., “Magnetic gold-nanorod/PNIPAAmMA nanoparticles for dual magnetic resonance and photoacoustic imaging and targeted photothermal therapy,” Biomaterials 34(22), 5651–5660 (2013).BIMADU0142-9612 http://dx.doi.org/10.1016/j.biomaterials.2013.03.085 Google Scholar

90. J. Shah et al., “Photoacoustic imaging and temperature measurement for photothermal cancer therapy,” J. Biomed. Opt. 13(3), 034024 (2008).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.2940362 Google Scholar

91. M. Pramanik et al., “Single-walled carbon nanotubes as a multimodal-thermoacoustic and photoacoustic-contrast agent,” J. Biomed. Opt. 14(3), 034018 (2009).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.3147407 Google Scholar

92. J. Zhang, T. Atay and A. V. Nurmikko, “Optical detection of brain cell activity using plasmonic gold nanoparticles,” Nano Lett. 9(2), 519–524 (2009).NALEFD1530-6984 http://dx.doi.org/10.1021/nl801891q Google Scholar

93. S. Chemla and F. Chavane, “Voltage-sensitive dye imaging: technique review and models,” J. Physiol. 104(1), 40–50 (2010). http://dx.doi.org/10.1016/j.jphysparis.2009.11.009 Google Scholar

94. F. F. Zhang et al., “Amperometric sensor based on ferrocene-doped silica nanoparticles as an electron transfer mediator for the determination of glucose in rat brain coupled to in vivo microdialysis,” J. Electroanal. Chem. 571(2), 133–138 (2004).JECHES0022-0728 http://dx.doi.org/10.1016/j.jelechem.2004.04.019 Google Scholar

95. J. Xia, C. Kim and J. F Lovell, “Opportunities for photoacoustic-guided drug delivery,” Curr. Drug Targets 16(6), 571–581 (2015). http://dx.doi.org/10.2174/1389450116666150707100328 Google Scholar

96. K. K. Jain, “Nanobiotechnology-based strategies for crossing the blood-brain barrier,” Nanomedicine 7(8), 1225–1233 (2012).1743-5889 http://dx.doi.org/10.2217/nnm.12.86 Google Scholar

97. W. M. Pardridge, “Blood-brain barrier delivery,” Drug Discovery Today 12(1–2), 54–61 (2007).DDTOFS1359-6446 http://dx.doi.org/10.1016/j.drudis.2006.10.013 Google Scholar

98. C. S. Yah, “The toxicity of gold nanoparticles in relation to their physiochemical properties,” Biomed. Res. 24(3), 400–413 (2013). Google Scholar

99. Y. L. Hu and J. Q. Gao, “Potential neurotoxicity of nanoparticles,” Int. J. Pharm. 394(1), 115–121 (2010).IJPHDE0378-5173 http://dx.doi.org/10.1016/j.ijpharm.2010.04.026 Google Scholar

100. C. Huang et al., “Full-wave iterative image reconstruction in photoacoustic tomography with acoustically inhomogeneous media,” IEEE Trans. Med. Imaging 32(6), 1097–1110 (2013). http://dx.doi.org/10.1109/TMI.2013.2254496 Google Scholar

101. S. N. Tabatabaei et al., “Remote control of the permeability of the blood-brain barrier by magnetic heating of nanoparticles: a proof of concept for brain drug delivery,” J. Controlled Release 206, 49–57 (2015).JCREEC0168-3659 http://dx.doi.org/10.1016/j.jconrel.2015.02.027 Google Scholar

102. H. Yuan et al., “Optically enhanced blood-brain-barrier crossing of plasmonic-active nanoparticles in preclinical brain tumor animal models,” Proc. SPIE 8935, 89350E (2014).PSISDG0277-786X http://dx.doi.org/10.1117/12.2040960 Google Scholar

103. M. Kolter et al., “Nanotoxicity of poly (n-butylcyano-acrylate) nanoparticles at the blood-brain barrier, in human whole blood and in vivo,” J. Controlled Release 197, 165–179 (2015).JCREEC0168-3659 http://dx.doi.org/10.1016/j.jconrel.2014.11.005 Google Scholar


Depeng Wang is currently a PhD student of biomedical engineering at the University at Buffalo. He received his bachelor’s and master’s degrees in engineering from Nanjing University of Aeronautics and Astronautics in 2012 and 2015, respectively.

Yun Wu received her PhD degree at The Ohio State University, and did postdoc training in the same university under the mentorship of Dr. Ly James Lee. She is currently an assistant professor in the Biomedical Engineering Department at the University at Buffalo and works on the development of therapeutic and diagnostic systems for the treatment and early detection of cancer and diseases. She has published more than 30 peer-reviewed journal articles in nanomedicine and bionanotechnology fields.

Jun Xia received his PhD at the University of Toronto and did his postdoc training at Washington University in St. Louis under the mentorship of Dr. Lihong V. Wang. Currently, he is an assistant professor in the Biomedical Engineering Department at the University at Buffalo. His research interests are the development of novel biomedical imaging techniques including photoacoustic imaging and ultrasonic imaging. He has published more than 30 peer-reviewed journal articles in photoacoustic and photothermal research.

© 2016 Society of Photo-Optical Instrumentation Engineers (SPIE)
Depeng Wang, Depeng Wang, Yun Wu, Yun Wu, Jun Xia, Jun Xia, } "Review on photoacoustic imaging of the brain using nanoprobes," Neurophotonics 3(1), 010901 (4 January 2016). https://doi.org/10.1117/1.NPh.3.1.010901 . Submission:

Back to Top