Combining optical excitation and acoustic detection, photoacoustic imaging (PAI) combines the high contrast available from optical imaging with the spatiotemporal resolution of ultrasound imaging. Conventional reporter genes (RGs) for optical imaging generate diffuse bioluminescence or fluorescence signals, which can be imaged with spatial resolutions that are typically comparable to, or worse than, the imaging depth.1,2 PAI transcends the depth limitations of optical imaging techniques that employ ballistic photons (Fig. 1) because acoustic waves are scattered far less than photons in tissue. The contrast in PAI arises due to optical absorption, for example by endogenous chromophores such as hemoglobin and melanin. However, to directly visualize most cellular and molecular processes, the image contrast must be provided by exogenous agents.3 A RG is an exogenous segment of DNA that encodes a protein product that, once expressed, can be visualized, either directly or indirectly, using imaging or chemical analysis. The application of RGs in optical imaging, magnetic resonance imaging (MRI), and nuclear medicine has been reviewed elsewhere.4,5 PAI RGs have been reviewed from the perspective of PAI technology;6 here, we provide a complementary practical guide to PAI RGs for the physical scientist, who may be unfamiliar with the biological background and the fundamental limitations. We highlight, in particular, the challenges of: biological RG production and characteristics (Sec. 3); spectral unmixing of the reporter signal (Sec. 4); and detection sensitivity (Sec. 5).
Principles of Photoacoustic Imaging
PAI starts with the excitation of molecules in biological tissues following absorption of photons from pulsed or modulated continuous-wave light sources. The excited molecules release the absorbed photon energy through nonradiative relaxation, inducing a small local temperature rise. This leads to a local pressure increase, which then relaxes resulting in the propagation of ultrasound (photoacoustic) waves throughout the tissue; these waves can be detected by ultrasonic transducers at the surface of the tissue.
PA image reconstruction essentially converts the detected time-resolved ultrasound signals back to the optical absorption distribution in space, a procedure similar to the Global Positioning System. This is a two-step problem involving first, reconstruction of the initial acoustic pressure distribution (the acoustic inverse problem) and second, recovery of the optical absorption distribution (the optical inverse problem). Various reconstruction approaches7 have been employed from the simplest and fastest method of back-projection,8,9 to more complex approaches that can account for arbitrary scanning geometries, such as model-based linear inversion,10 iterative methods,11 time-reversal, and fast Fourier transform-based methods.12,13 Solution of the optical inverse problem for accurate quantification of the optical absorption distribution remains challenging14 but is essential for quantitative molecular imaging (discussed further in Sec. 4).
PAI is a highly scalable imaging modality, achieving different spatial resolutions and imaging depths based on different configurations of: light sources; ultrasonic detection systems; and scanning mechanisms.15,16 Based on the image formation method, PAI can be roughly classified into: photoacoustic microscopy (PAM) with single-element ultrasonic detection and direct image formation; or photoacoustic computed tomography (PACT) with multielement ultrasonic detection and inverse image reconstruction (see Fig. 2). Both image resolution and tissue attenuation scale with increasing ultrasound detection frequency. In general, PAM, with high-frequency ultrasound detection at tens of MHz, provides micron-resolution images with penetration depths up to several millimeters, whereas PACT, with low-frequency ultrasound detection at a few MHz, is capable of deep-tissue imaging with centimeter penetration and submillimeter resolutions.
Genetic Reporters used in Photoacoustic Imaging
Production of Cells Expressing Reporter Proteins
The production of genetically modified mammalian cells involves transfection, which is the general term describing a procedure for introducing foreign nucleic acids, such as those constituting a RG, into eukaryotic cells. Transfection methods can be broadly categorized into those that are transient and others that are stable, illustrated in Figs. 3(a) and 3(b) respectively. Transient transfection (TT) is relatively straightforward, involving the introduction of DNA into cells along with an agent that promotes its uptake. However, since the foreign DNA is not integrated into the host genome, the sequence is gradually lost after repeated cell divisions leading to gene expression that lasts only a few days. Alternatively, stable transfection entails integration of the foreign genetic material into the host genome giving rise to long-term expression of the sequence of interest as it is propagated in subsequent cell generations.
Methods for TT are generally physical or chemical.17 The most commonly used physical method is electroporation, which can rapidly transfect large numbers of cells, but only after an experimentally demanding determination of the optimum conditions. PAI studies to date have predominantly used chemical methods for TT. These methods include use of a cationic liposome,18 a cationic lipid,19 or calcium phosphate,20 and are widely available but may vary in their toxicity and efficiency according to the cell type. The RG can be coexpressed with an antibiotic resistance gene and/or a fluorescent marker such as EGFP or an inert membrane tag such as the truncated nerve growth factor receptor (dNGFR). These enable successfully transfected cells to be selected by their survival in the presence of antibiotic, and also the reporter protein expression level to be identified using flow cytometry of the coexpressed marker.
Stable transfection typically involves virus-mediated gene delivery,21 which is also known as transduction. The first step in the transduction process is to transfect three or four plasmids—one envelope vector, one or two packaging vectors, and the transfer vector containing the RG—into packaging cells such as human embryonic kidney 293T cells (HEK293T). The virus is then harvested from these cells and used to infect the target cells, resulting in incorporation of the RG sequence into the host DNA. Photoacoustic RG studies have employed common viral vectors including lentiviruses20,22 and retroviruses.23,24 Lentiviruses are more versatile since they transduce nondividing cells, unlike retroviruses, which require replicating cells for transduction. A third viral vector system that has been used is the vaccinia virus,25 but this is limited to transient protein production since the virus replicates in the cytoplasm outside the nucleus and the infected cells only survive for one or two days.
Classes of Reporters
PAI RGs can be classified as indirect (enzymatic, which result in nonfluorescent proteins, Sec. 3.3) or direct (fluorescent and nonfluorescent proteins, Sec. 3.4). These classes are shown in Fig. 4, and their spectra are given in Fig. 5. Enzymatic RGs provide inherent signal amplification, as a single enzyme can create multiple molecules of absorbing product, whereas direct RGs provide stoichiometric mapping between the amount of detected protein and the level of RG expression. Table 1 makes further comparisons between the different classes of reporters. The ideal reporter should be: specific to the biological process of interest; exhibit an absorption maximum in the tissue optical window for deep in vivo imaging; be nontoxic to the cell; and avoid photobleaching. The reviewed RGs, including optical properties and demonstrated applications, are discussed in the following two sections and summarized in Table 2.
Summary of the key features of different groups of RGs investigated in PA imaging.
|Indirect reporters (enzymatic):|
|✗||Low absorption coefficient, but…|
|✓||Inherent signal amplification: one enzyme molecule can create multiple molecules of absorbing product|
|✓||Not susceptible to photobleaching|
|Direct reporters (nonenzymatic):|
|✓||Provide mapping between the detected protein and the RG expression|
|– GFP-like fluorescent proteins:|
|✗||Susceptible to photobleaching|
|✗||Absorption maxima typically overlap with high blood attenuation, preventing deep tissue imaging|
|– Fluorescent proteins from phytochromes:|
|✗||Typically require a cofactor (although this is not a problem in mammals)|
|✓||Less susceptible to photobleaching|
|✓||Allow deep tissue imaging (absorption in the NIR)|
|– Nonfluorescent proteins (chromoproteins):|
|✗||Not yet efficiently expressed in mammalian cells|
|✓||Not susceptible to photobleaching;|
|✓||High PA signal generation efficiency|
|– Photoswitchable proteins:|
|✓||Reversibly photoconvertible between red and NIR absorption states; image subtraction improves contrast, background removal, and spatial resolution|
|✓||NIR absorption for deep tissue imaging|
|✓||No photobleaching even at fluences above the MPE|
Note: NIR, near-infrared; MPE, maximum permissible exposure.
Properties of genetic reporters used in PAI.
|Reporter protein and source||Absorption max., λmax (nm)||Molar ext. coefficient, ε (M−1 cm−1)||Fluorescence quantum yield, ϕf (%)||References for λmax, ε, ϕf demonstrated applications|
|Eumelanin||Tyrosine—tyrosinase||No clear max. (Fig. 5)||—||41|
|• MCF-7-TYR cells, DOX-inducible melanin expression: in vitro US/PACT B-scans and MRI;18 s.c. injection of cells into mouse back flanks, multi- PACT.47 • s.c. injection of MCF-7-TYR cells (not DOX-inducible) in into mouse shoulder, 680-nm PACT.48 • TYR inserted into vaccinia virus strain GLV-1h68 used to treat and image three tumor cell lines implanted in mice.25 • s.c injection into nude mouse ear of HEK293-TYR cells in , OR-PAM.71 • s.c injection into nude mouse flank of K532-TYR or 293TTYR cells, longitudinal FP PACT; s.c injection into nude mouse abdomen of K532-TYR, 8-mm deep FP PACT24|
|• of Vio-expressing E. coli injected into 4T1 tumor xenografts, MSOT imaging9|
|5,5′-Dibromo-4,4′-dichloroindigo||X-gal—-galactosidase (from lacZ gene)||655||10,600||—||42|
|• First demonstration of RGs in PAI.44 s.c. injection into rat scalp of 5M 9L gliosarcoma cells expressing lacZ gene; X-gal () injected 1 day before imaging. Dual wavelength AR-PAM,42,45 OR-PAM,45 and PACT45|
|Permanently fluorescent reporters|
|Aequorea victoria||• Salivary glands of fruit y Drosophila melanogaster, MSOT, spectrally resolved;26 • in vitro comparison of PA signal generation efficiency with 63|
|Discosoma striata||• In vitro HeLa-DsRed cells (), MSOT, spectrally resolved;26 • in vitro measurement of PA spectrum and photobleaching23|
|Discosoma striata||• Vertebral column of transgenic adult zebrafish, MSOT, spectrally resolved;26 • in vitro measurement of PA spectrum and photobleaching;23 • in vitro comparison of PA signal generation efficiency with 63|
|Entacmaea quadricolor||• In vitro PACT;62 • in vitro comparison of PA signal generation efficiency with 63|
|Actinia equina||• In vitro measurement of PA spectrum and photobleaching23|
|Discosoma striata||• In vitro measurement of PA spectrum and photobleaching;23 • in vitro comparison of PA signal generation efficiency with 63|
|Entacmaea quadricolor||• In vitro PACT;62 • in vitro measurement of PA spectrum and photobleaching;23 • in vitro PACT;65 • in vitro comparison of PA signal generation efficiency with 63|
|Entacmaea quadricolor||• In vitro PACT;62 • in vitro PACT;65 • in vitro comparison of PA signal generation efficiency with 63|
|Discosoma striata||• In vitro PACT;62 • in vitro measurement of PA spectrum and photobleaching;23 • in vitro PACT;65 • in vitro comparison of PA signal generation efficiency with ;63 • exocrine pancreas of transgenic adult zebrafish, Fabry–Perot PACT and SD-OCT55|
|Entacmaea quadricolor||• In vitro PACT;62 • in vitro comparison of PA signal generation efficiency with 63|
|Rhodopseudomonas palustris phytochrome: RpBphP6||• First demonstration of PACT with two NIR genetic reporters: MTLn3-iRFP670 and MTLn3-iRFP720 cells injected into mouse mammary gland ( to ), s, two different PAT implementations65|
|Rhodopseudomonas palustris phytochrome: RpBphP2||• The first application of a NIR FP in PACT: 1 M MTLn3-iRFP cells injected into mouse mammary gland, PACT and PAM;62 • MTLn3-iRFP injected into mouse tail vein and detected in mouse ear using multimodal PA-fluorescence flow cytometry (PAFFC);73• in vitro PACT;65 • U87-iRFP cells mouse brain tumor, MSOT, comparison with different imaging modalities;63 • mouse brain tumor, MSOT, different unmixing methods64|
|Rhodopseudomonas palustris phytochrome: RpBphP2||• First demonstration of PACT with two NIR genetic reporters: MTLn3-iRFP670 and MTLn3-iRFP720 cells injected into mouse mammary gland ( to ), s, two different PACT implementations65|
|Nonfluorescent proteins (chromoproteins)|
|Discosoma striata||• In vitro measurement of PA spectrum and photobleaching23|
|aeCP597||Sea anemone:||597||110,000||—||31 and 23|
|Actinia equina||• In vitro measurement of PA spectrum and photobleaching23|
|Cnidopus japonicus||• In vitro measurement of PA spectrum and photobleaching;23,68 PA-based screening for a variant (cjBlue2) with > twofold enhancement in PA signal, and a slight blue shift68|
|Montipora efforescens||• In vitro measurement of PA spectrum and photobleaching; PA-based screening for a variant (tdUltramarine2) with three- to fourfold enhancement in PA signal; in vitro dual-wavelength PA assessment of tdUltramarine2 as a FRET acceptor; in vivo imaging of E. coli cells expressing Ultramarine or tdUltramarine2 injected into the rat ear68|
|Dronpa||Coral:||ON||503||9500||85.0||74 and 75|
|Pectiniidae||OFFx||390||Not given||2.0||• Temporal unmixing of fast-switching Dronpa-M159T and the slower-switching wildtype Dronpa using the purified proteins in a phantom imaged using MSOT; unmixing of E. coli expressing Dronpa-M159T from blood in a phantom;70 used for lightfluence correction76|
|Entacmaea quadricolor||OFF||440||15,300||0.1||• In vitro analysis of photoswitching rate and CNR, 567 nm OFF → ON switching wavelength19|
|Rhodopseu-domonas palustris||Pr (OFF)||678||87,500||—||• Injection of U87-BphP1 cells into kidney and mouse brain, single differential method for high sensitivity, longitudinal PACT imaging of liver metastases, super-resolution PAM, 780-nm OFF → ON switching wavelength19|
|AGP1||Bacterium:||Pfr (ON)||750||40,000||—||78 and 22|
|Agrobacterium tumefaciens||Pr (OFF)||701||94,000||—||• s.c. injection of HT29-AGP1 cells into nude mice, Fabry–Perot PACT, 670-nm OFF → ON switching wavelength22|
Note: AR-PAM, acoustic resolution photoacoustic microscopy; CNR, contrast-to-noise ratio; DOX, doxycycline; FP, fluorescent protein; λ, wavelength; M, million; MRI, magnetic resonance imaging; MSOT, multispectral optoacoustic tomography; NIR, near-infrared; OR-PAM, optical resolution photoacoustic microscopy; PA, photoacoustic; PACT, photoacoustic computed tomography; PAI, photoacoustic imaging; s.c., subcutaneous; SD-OCT, spectral domain optical coherence tomography; US, ultrasound imaging. ε, molar extinction coefficient at the wavelength of absorption maximum λmax.
Three enzymatically generated reporters have been introduced for PAI: (1) 5,5′-dibromo-4,4′-dichloroindigo, a blue precipitate produced via the enzyme -galactosidase (encoded by the lacZ gene), which metabolizes X-gal; (2) eumelanin, a brown pigment produced through action of the tyrosinase enzyme on tyrosine; and (3) violacein, a violet pigment produced from L-Tryptophan via the action of a five-enzyme operon.
LacZ. LacZ is the earliest example of a PAI reporter.44 It expresses -galactosidase, an Escherichia coli enzyme involved in the metabolism of lactose. Injection of X-gal, a colorless analogue of lactose, leads to formation of a blue product (5,5′-dibromo-4,4′-dichloroindigo) after cleavage by -galactosidase [Fig. 6(a)]. The blue product is strongly absorbing between 600 and 700 nm. Dual-wavelength PAM42,45 and PACT45 have been used to detect gliosarcoma cells expressing the lacZ gene under the rat scalp; however, X-gal requires local administration as systemic delivery is inefficient,44 which has discouraged further PAI studies with the lacZ gene.
Tyrosinase. Tyrosinase oxidizes tyrosine to dopaquinone, which then undergoes several reactions that lead to melanin pigments [Fig. 6(b)]46 including eumelanin and pheomelanin. Eumelanin exhibits a broad extinction coefficient spectrum (similar to that of pheomelanin), with absorption extending into the near-infrared, enabling it to be detected above the background hemoglobin signal at wavelengths between 600 and 700 nm.18,24,47 Paproski et al.18 were the first to develop tyrosinase as an RG for PAI. They subsequently developed an inducible system, in which tyrosinase expression was triggered by doxycycline administered in the animals’ drinking water.47 The tyrosinase reporter has also shown multimodal imaging potential48 as eumelanin can bind heavy metal ions () detectable with MRI, and a melanin-targeted -P3BZA probe for positron emission tomography. Stritzker et al.25 also explored multimodal tyrosinase imaging by TT of tumor bearing mice with a vaccinia virus encoding tyrosinase. This approach offers clinical relevance but prevents longitudinal studies. To maintain tyrosinase expression in subsequent generations of cells requires modification of the cell genome, which, although ethically unapproved for clinical studies, does allow longitudinal animal imaging. Jathoul et al.24 achieved this using stable retroviral transduction, which enabled tumor growth to be monitored over periods up to 52 days, with apparently little effect on cell viability [Fig. 4(a)].
Violacein. The deep violet chromophore violacein is enzymatically generated [Fig. 6(c)] from the sole precursor tryptophan by five enzymes (VioA-E) that were originally cloned from Chromobacterium violaceum. Violacein has a strong absorption peak around 575 nm, enabling differential detection through dual-wavelength excitation at 490 and 650 nm. However, while tyrosinase and lacZ have been expressed in mammalian cells, the violacein operon has so far only been expressed in bacteria.50 Violacein may, therefore, find application for in vivo imaging of bacterial infections or theranostic applications, but concerns remain about the toxicity to mammalian cells.
Nonenzymatic Reporters: Fluorescent, Nonfluorescent, and Photoswitchable Proteins
Nonenzymatic reporters can be classified by their optical properties and according to their natural origins, such as marine creatures and bacteria [Figs. 5(a)–5(c), Fig. 7]. In general, nonfluorescent proteins are preferable since they exhibit higher photoacoustic generation efficiency and significantly higher photostability (Fig. 8).
Since the discovery of green fluorescent protein (GFP), fluorescent proteins have been widely applied in biomedical studies, mostly imaged by fluorescence microscopy.27,51,52 GFP-like proteins are derived from anthozoa (such as sea anemones and corals) or scyphozoa (jellyfish) and have a common structure consisting of a -barrel scaffold containing the chromophore, which is formed by folding of the polypeptide chain.53 Within the barrel the chromophore is protected from the outside environment, making it possible to genetically engineer the chromophore microenvironment, for example, to produce enhanced brightness (EGFP)54 or spectral modifications. Razansky et al.26 reported the first demonstration of PAI using EGFP and mCherry in fruit fly and adult zebrafish [Fig. 4(b)]. The absorption peaks of even the furthest red-shifted GF homologues35,55 are generally restricted to the visible wavelength region, making them well suited to PAM but less applicable for PACT deep in vivo imaging [Fig. 5(a)].
In recent years, several near-infrared fluorescent proteins (IFPs) have been derived from bacterial phytochrome photoreceptors (BphPs).56 These are targeted toward deep tissue in vivo imaging, exploiting the optical window where endogenous chromophores have relatively low absorption between 620 and 950 nm [Fig. 5(d) and 5(e)]. BphPs incorporate a far-red absorbing bilin, biliverdin (BV), as their chromophore, which is ubiquitous in most eukaryotic organisms. The overall structure of the BphP photosensory module consists of two or three protein domains linked by -helices (Fig. 9), which may exist as a monomer, dimer, or oligomer. As with GFP-like proteins, monomers are preferable and several monomeric IFPs have been developed.5758.–59 Compared to GFP-like proteins, BphPs exhibit several advantages for PAI,60 such as a relatively low fluorescence quantum yield ( for iRFP compared to 60% for EGFP) and a high intrinsic extinction coefficient ( for iRFP, compared to for EGFP).
The BphP iRFP713 (also known as simply iRFP61) was the first to be demonstrated in PAI. iRFP expressed in tumor cells inoculated in the mammary fat pad efficiently incorporated endogenous BV, and an imaging depth of 4 mm was achieved exploiting the peak iRFP absorption of 690 nm.62 Two subsequent studies at similar penetration depths imaged mouse brain tumors expressing iRFP71363,64 and illustrated spectral resolution of two variants of iRFP (iRFP670, 645 nm peak and iRFP720, 702 nm peak37) as well as background hemoglobin signals.65 Despite this improved penetration depth of imaging compared to GPF-like fluorescent proteins, the photostability of BphPs remains low, due not only to photobleaching but also to transient absorption effects.66,67 Furthermore, while their low fluorescence quantum yield is attractive for PAI, fluorescent emission and ground state depopulation can lead to low PA signal generation efficiency. This may partly explain the observed discrepancies between the measured absorption and photoacoustic spectra of these proteins.23
Nonfluorescent proteins (chromoproteins)
Challenges with photobleaching and low PA signal generation has led to efforts to develop nonfluorescent (or very weakly fluorescent) proteins, also called chromoproteins [Fig. 5(b)]. Those reported to date are a subset of GFP-like proteins, which have been identified in Anthozoa species31,38,39 or mutated from their fluorescent equivalents.23 Chromoproteins exhibit higher PA signal generation efficiency due to the absence of radiative relaxation and ground state depopulation, as well as significantly higher photostability (Fig. 8).23,68 PAI of the chromoprotein reporter ultramarine has been demonstrated in vivo68 in the rat ear.
Photoswitchable proteins undergo a change in their absorption spectra under illumination with a specific wavelength [Fig. 5(c)]. The mechanism behind this change is typically a cis-trans isomerization of the chromophore. For the BV chromophore used in BphPs, the two conformations are referred to as Pr (“pigment red absorbing,” also termed the OFF state) and Pfr (“pigment far-red absorbing,” or the ON state)56 (Fig. 10). In the unbound state, switching does not affect the absorption properties of BV, but when covalently bound to the protein barrel the two isomeric states exhibit distinct absorption spectra. This property has been exploited in a comprehensive study of a photoswitchable protein BphP1 derived from the bacterial phytochrome RpBphP1.19 By taking the pixelwise subtraction between the images of the protein in the OFF and ON states, a fold enhancement in the contrast-to-noise ratio (difference between proteins and blood) was obtained relative to the ON-state image. This differential imaging enabled visualization of BphP1-expressing U87 cells in the left kidney in PACT at depths up to , with an average CNR of . The photoswitching property was exploited to perform subdiffraction imaging of individual cells in PAM, as BphP1 molecules are switched off at a rate proportional to the local excitation intensity, which is greater in the centre of the Gaussian-shaped laser pulse than at the periphery. In addition to this study, which illustrates the versatility of photoswitchable proteins for high contrast in vivo imaging, a preliminary demonstration has recently emerged of a second BphP derived photoswitchable protein, AGP1.22 Various photoswitchable proteins have also been derived from corals (GFP-like),69 two of which have been demonstrated for PAI: rsTagRFP19 and Dronpa.70 With absorption peaks at wavelengths , these proteins are most suitable for studies in PAM.
Recovering the Spatial Distribution of Genetic Reporters
Compared to fluorescence imaging of RGs, PAI can be easily performed at multiple wavelengths to specifically resolve the spatial distribution of overlapping absorption spectra. Nonetheless, achieving such spectral resolution through mathematical “unmixing” procedures is nontrivial since there are multiple endogenous absorbers present in tissue that also contribute to the signal. The position () and wavelength () dependent absorption coefficient may be written as the sum of the individual molar extinction coefficients of the contributing chromophores with molar concentrations ,47 giving a direct proportionality between the absorbed energy density map and the detected PA signal . However, is the product of the fluence , which itself varies as a function of and , as well as and the reduced scattering coefficient Table 3): (1) peak wavelength imaging; (2) spectral unmixing; or (3) difference imaging. The first approach simply maps the spatial distribution of signals above the background at a wavelength where the absorption of the chromophore of interest is high, but the background absorption dominated by the hemoglobins is relatively low.18,24,44,45,48,50 The latter approaches are more complex, as discussed below.
Summary of methods used to separate chromophores in PA imaging.
|Method||Details, advantages, ⊕ and disadvantages ⊖||References|
|Peak imaging||Maps by thresholding signals at a where the chromophore background absorption||18, 24, 44, 45, 48, and 50|
|⊕ Simple to implement and fast to compute|
|⊖ Arbitrary threshold; signal may be lost in background|
|Linear inversion||is divided by ; chromophores are then separated by least squares regression|
|• calculated||Assumes homogeneous background optical properties||26 and 62|
|⊕ Simple to implement and fast to compute|
|⊖ Limited accuracy for nonsuperficial tissue layers||79|
|• determined experimentally||⊕ Potential for to accurately estimate|
|⊖ No approach seems practical for in vivo measurements:|
|→ Black absorber inserted invasively||80 and 81|
|→ DOT only gives a low resolution fluence map||82|
|→ Poor speckle contrast for AO assisted fluence correction||83|
|• modeled and recovered iteratively||Light transport model using assumed and initialized to give and ; iterative optimization relative to|
|→ Simulations, phantoms, and in vivo studies have used the RTE, or its diffuse approximation||8485.86.87.–88|
|⊕ Potential for to accurately estimate|
|⊖ Distribution of is often unknown in vivo|
|Nonlinear model-based inversion||Iterative search for combinations of and that minimize the difference between and||89 and 90|
|⊕ General method for recovery of absolute|
|⊕ Little prior information required|
|⊖ Nonunique values for give identical|
|requiring workarounds such as multiple illuminations||9192.–93|
|⊖ Many variables, occupying extensive computer memory|
|Semiquantitative, blind unmixing||Use statistical properties of chromophore distributions to unmix relative contributions rather than absolute|
|→ Vertex component analysis||94|
|→ AMF||95 and 96|
|→ ICA||63 and 98|
|⊕ Can provide more accurate results than linear inversion|
|⊕ Easy to implement and low computational cost|
|⊖ Requires correction for spectral coloring|
|⊖ Cannot estimate absolute|
|Novel decomposition methods||Separate from without using light transport models|
|⊕ No fluence modeling required;|
|⊖ Usually complex; not yet generally applicable in vivo|
|→ Sparse representations based on spatial characteristics||99|
|→ Linear superposition of reference fluence base spectra||100|
|→ “Differential” PA signal generated by two different||101|
|Difference imaging||Pixelwise subtraction of images acquired with a photoswitchable reporter in two different absorption states||19, 22, 70, and 76|
|⊕ No knowledge of the fluence required|
|⊕ Enables resolution enhancement in OR-PAM||19|
|⊖ Only possible for photoswitchable reporters|
Note: AO, acousto-optics; DOT, diffuse optical tomography; RTE, radiative transport equation. ck(r), chromophore concentrations; H(r,λ), absorbed energy density; Hest, estimated H(r,λ); λ, wavelength; μa, absorption coefficient; μs′, reduced scattering coefficient; ϕest, estimated fluence. AMF (adaptive matched filter), PCA (principal component analysis), and ICA (independent component analysis).
Spectral unmixing takes advantage of the multiwavelength data acquisition capability of PAI, applying multivariate analysis techniques to retrieve abundance maps of the individual absorbers present in the tissue (Fig. 11). First, the aforementioned challenge of unknown light fluence must be accounted for, which is usually achieved with the addition of a preprocessing step. Multiwavelength PA data are typically divided by an estimated value of the fluence to give images proportional to . For imaging of the superficial tissue layers in PAM, the light fluence may be assumed to be spectrally constant71 and can be estimated experimentally, for example, by invasively inserting a film with uniform absorption to correct for absorption by the dermis.80,81 For applications in PACT, a simple finite-element method solution to the light diffusion equation assuming homogeneous background optical properties can be applied to derive .26,55,62,65 More rigorous approaches to deal with this “spectral coloring” in PACT include Monte Carlo simulations and model-based iterative minimization;84220.127.116.11.89.–90 however, these methods are computationally intensive and may give rise to nonunique solutions. As a result, they are not routinely applied during in vivo imaging.
Having dealt with the data preprocessing, most RG studies perform linear inversion using a form of least-squares regression,26,55,62,65 in some cases with constraints for positive concentration values exceeding some threshold.47,68 These least-squares approaches rely on a priori knowledge of the absorption spectra present within a given voxel. Where these are not well known, for example, when the spectra change as a function of concentration, semiquantitative “blind” methods that use the inherent statistical properties of the spectral data can be employed. Some examples relevant to RG imaging include: principle component analysis (PCA);97 independent component analysis (ICA);63,98 vertex component analysis;94 and adaptive matched filter (AMF).64,95 Only AMF64 and ICA63 have been applied in PAI of RGs; both methods were able to resolve brain tumors in mice expressing iRFP713. Tzoumas et al.64 assessed the impact of the number of excitation wavelengths and different unmixing algorithms on the detection sensitivity for the RG, although their findings contradict prior studies suggesting that the optimum number of wavelengths and unmixing algorithm is likely to be case sensitive.95
Spectral unmixing is hampered by fundamental requirements: the preprocessing must be accurate to compensate for light fluence, and the data must have sufficient signal-to-noise ratio (SNR) to avoid corruption of the spectral profile. The recent emergence of photoswitchable nonfluorescent proteins [Fig. 4(c), Sec. 3.4]19,22,70 mitigates these limitations by switching the protein ON/OFF state between image acquisitions. Taking the difference of images acquired at the same wavelength but with different protein states effectively eliminates the nonswitchable background signals, minimizing the effect of the local optical fluence.76 As a result, photoswitchable reporters achieve reliable background removal and have been shown to dramatically enhance the detection sensitivity (-fold enhancement in contrast-to-noise ratio compared to two-wavelength least-squares fitting19). For applications requiring quantification of protein concentration, rather than only qualitative spatial localization, photoswitchable reporters therefore represent an ideal solution.
The ability to detect and resolve RGs in vivo relies on sufficient sensitivity in the PAI hardware, as well as biological considerations, such as gene expression levels and spectral characteristics of the reporter.
Imaging System Sensitivity
For molecular PAI, spatial resolution and penetration depth have to be traded to optimize the detection sensitivity. One parameter used to quantify detection sensitivity is the noise-equivalent detectable concentration (NEC).79 NEC is calculated as the concentration of the imaged molecules normalized by the SNR. To achieve a low NEC, one can increase the excitation light fluence (within the maximum permissible exposure, MPE) to increase the SNR. Since the SNR of PAI is proportional to the total number of molecules in a resolution voxel, relaxing the spatial resolution can also improve the NEC, as long as the local optical fluence is maintained. Counter-intuitively, this means that PACT systems, which generally have worse spatial resolution, typically have a better NEC than PAM systems, provided that the light pulse energy is sufficient.
The detection sensitivity of PAI is generally lower than that of pure optical imaging modalities by at least two orders of magnitude.79 This is somewhat surprising considering that, at the source (the imaged target), the overall energy conversion efficiencies of fluorescence and PA imaging are similar: for a fluorescent absorber, the transfer of energy from the absorbed photons to fluorescent emission is typically less than 30% efficient, determined by the fluorescent quantum yield, and the remaining absorbed optical energy is deposited as thermal energy, which is subsequently converted to acoustic energy with an efficiency of at body temperature, determined by the Grüneisen coefficient.82 The difference in sensitivity between the two imaging modalities is largely a consequence of the detectors. While a photomultiplier tube used in fluorescence imaging may have single-photon sensitivity, a typical ultrasonic transducer has a noise-equivalent pressure (NEP) of ,83,91 which is equivalent to a temperature rise at the target of . Within the skin MPE (), the noise equivalent absorption coefficient () of the target is . For EGFP with a molar extinction coefficient of and quantum yield of 60% at 488 nm, this roughly translates to an NEC of . When the geometric signal loss from the target to the ultrasonic transducer is taken into account,91,92 the NEC approaches several micromolars, which is generally consistent with experimental results and much higher than that of native proteins in cells.79 By contrast, the detection sensitivity of fluorescence microscopy is on the level of several nanomolars, close to the natural concentrations of native cell components.
Fundamental limitations on recorded PA signals are: PA detection sensitivity; PA signal generation efficiency; and the tissue optical and acoustic attenuation. Fortunately, the acoustic sensitivity of ultrasound detectors can be enhanced by better matching their detection bandwidth with the broadband PA signal spectrum. While the detection sensitivity of a conventional piezoelectric ultrasonic transducer degrades with decreasing element size, the sensitivity of optical sensors of acoustic waves, typically based on interferometry, does not. Therefore, optical detection holds promise for high-sensitivity PACT, especially for the cases where the elements of the ultrasonic transducer array are miniaturized to achieve isotropic resolutions.93,96,99
For PAI at depths more than 1 mm, the reporter protein should have an absorption maximum within the tissue optical window (620 to 950 nm) where mammalian tissues are relatively transparent due to the low optical absorption by water, lipids, hemoglobin, and melanin. Even with such optimization of the reporter protein absorption wavelength, the strong background signal from blood still presents a challenge for PA RG imaging, since hemoglobin concentration in tissue is .100 The problem is shown in Figs. 5(d) and 5(e), which compares the molar extinction spectra and specific extinction spectra for the hemoglobins and a selection of enzymatic and direct PAI reporters. The molecular mass of enzymatically produced proteins is more than two orders of magnitude smaller than the molecular mass of the hemoglobins and directly produced proteins, such as mCherry or BphP1. Thus, care must be taken when comparing required reporter concentrations in terms of moles, grams, or gene-expressing cell numbers. As an example of the challenges of reporter detectability, while the absorption maximum of BphP1 is in the tissue optical window, if the protein concentration is two orders of magnitude lower than hemoglobin concentrations, it remains a challenge to detect a signal above the hemoglobin background. Nonetheless, proteins derived from bacterial phytochromes (iRFP670 and iRFP720) have been detected at estimated concentrations in vivo of 16 to ,65 although the effect of such high concentrations on cell biology remains unknown.
RGs for PAI have the potential to be applied in a variety of fundamental biomedical studies that require high spatial resolution at extended penetration depths. Examples include but are not limited to: (1) visualizing the expression of genes of interest; (2) understanding signal transduction pathways and protein–protein interactions;101 (3) longitudinal monitoring of tumor growth,24,19 (4) tracking the in vivo distribution of administered cells (e.g., therapeutic immune cells); (5) probing distance-dependent interactions between two proteins (Förster resonance energy transfer);68 and (6) reporting on environment change due to biochemical activities (e.g., calcium ion concentration). Furthermore, complementing functional PAI of neuronal activities in deep brain () using hemoglobin signals,103 novel genetic reporters of action potentials or surrogates (e.g., voltage-, or calcium-sensitive proteins) would be of great advantage104 and could potentially be engineered from nonfluorescent near-infrared BphPs.105 An additional future area of interest could be development of PAI optogenetic sensors to modulate neuronal activities in deep brain, where the light-mediated control of protein–protein interactions could be monitored at high resolution.106
Challenges and Prospects
PAI has filled a void of high-resolution optical imaging in deep tissue, opening the potential for biomedical studies that require high-resolution RG imaging at depths beyond the optical diffusion limit. Moreover, the use of nonionizing radiation in PAI allows longitudinal molecular imaging of the same animal, enabling informative observations of disease progression or drug efficacy. The properties of existing reporters are compared in Table 1. Chromoproteins are promising given their high PA signal generation efficiency but have not yet been expressed efficiently in mammalian cells. So far, despite requiring tailored instrumentation, photoswitchable proteins show the greatest potential for deep tissue in vivo PA imaging, since differential imaging between ON/OFF states removes the endogenous background signal improving image contrast and SNR.
The major challenges in PAI of RGs are sensitivity and quantification. The detection sensitivity is ultimately limited by the instrumentation but can be somewhat mitigated by choosing reporters with favorable absorption characteristics and high protein expressions levels. Recovering the spatial distribution of reporters has been approached using two distinct methods. Spectral unmixing results in large uncertainties and false positives, mainly due to the unknown light fluence. Using photoswitchable phytochromes is potentially only limited by detection noise. Both approaches remain susceptible to motion artifacts, which can be overcome by minimizing the time interval between image acquisitions.107108.–109 The focus for future studies should be to optimize detection sensitivity and to improve reporter localization and quantification. This requires technical improvements in acoustic transducer sensitivity, and addressing signal unmixing challenges such as the unknown light fluence. Further biological improvements could develop and optimize the spectra and extinction coefficients of photoswitchable reporters applied in difference imaging.
The number of RGs for PAI has expanded dramatically in recent years with examples of high-resolution and high-sensitivity detection of reporter proteins now available. Future developments in PAI hardware and protein engineering will push the current detection limits further, enabling PAI to emerge as a modality of choice for longitudinal molecular imaging of genetic reporters.
The authors have no relevant financial interests in this article and no other potential conflicts of interest to disclose.
The authors would like to thank Amit Jathoul for helpful discussion. J.B. and S.E.B. are supported by the EPSRC-CRUK Cancer Imaging Centre in Cambridge and Manchester (No. C197/A16465); CRUK (Nos. C14303/A17197 and C47594/A16267); and the European Union’s Seventh Framework Programme (No. FP7/2007-2013) under Grant Agreement No. FP7-PEOPLE-2013-CIG-630729. J.Y. is partly supported by Duke MEDx Basic Research Grant. J.L. acknowledges the support of ERC Starting Grant No. 281356.
Joanna Brunker received her MSc degree in natural sciences and her PhD in medical physics and biomedical engineering from the University College London, UK. She is a postdoctoral research fellow at the Cancer Research UK Cambridge Institute. Her research interest is the engineering of reporters and the development of instrumentation for functional photoacoustic imaging, with a focus on tumor hypoxia.
Junjie J. Yao received his BE and ME degrees from Tsinghua University and his PhD in biomedical engineering from Washington University, St. Louis. He is an assistant professor of biomedical engineering at Duke University and a faculty member of Duke Center for In Vivo Microscopy and Fitzpatrick Institute for Photonics. His research interest is in photoacoustic tomography technologies in life sciences, especially in functional brain imaging and early cancer detection.
Jan Laufer graduated as a diplom-ingenieur in biomedical engineering from the University of Applied Sciences Lbeck and received his PhD in medical physics from the University College London, UK. He is a professor of medical physics at the Martin-Luther-Universitä Halle-Wittenberg, Germany. His research interest is the development of methods and technologies for molecular and functional photoacoustic imaging.
Sarah E. Bohndiek received her BA degree from the University of Cambridge and her PhD in radiation physics from the University College London. She is a group leader in biomedical physics at the University of Cambridge. Her research is focused on the development of innovative optical imaging techniques to enable earlier diagnosis of cancer.