Emerging applications of porphyrins in photomedicine

Huang, Haoyuan; Song, Wentao; Rieffel, James; Lovell, Jonathan F.

doi:10.3389/fphy.2015.00023

REVIEW article

Front. Phys., 10 April 2015

Sec. Medical Physics and Imaging

Volume 3 - 2015 | https://doi.org/10.3389/fphy.2015.00023

This article is part of the Research Topic Imaging and Spectroscopy to Guide Photodynamic Therapy Optimization View all 7 articles

Emerging applications of porphyrins in photomedicine

$\r\nHaoyuan Huang$ Haoyuan Huang

Wentao Song

James Rieffel

Jonathan F. Lovell^*

Department of Biomedical Engineering, University at Buffalo, State University of New York, Buffalo, NY, USA

Biomedical applications of porphyrins and related molecules have been extensively pursued in the context of photodynamic therapy. Recent advances in nanoscale engineering have opened the door for new ways that porphyrins stand to potentially benefit human health. Metalloporphyrins are inherently suitable for many types of medical imaging and therapy. Traditional nanocarriers such as liposomes, dendrimers and silica nanoparticles have been explored for photosensitizer delivery. Concurrently, entirely new classes of porphyrin nanostructures are being developed, such as smart materials that are activated by specific biochemicals encountered at disease sites. Techniques have been developed that improve treatments by combining biomaterials with photosensitizers and functional moieties such as peptides, DNA and antibodies. Compared to simpler structures, these more complex and functional designs can potentially decrease side effects and lead to safer and more efficient phototherapies. This review examines recent research on porphyrin-derived materials in multimodal imaging, drug delivery, bio-sensing, phototherapy and probe design, demonstrating their bright future for biomedical applications.

Introduction

The red color of heme in blood has served as a marker for injury for hundreds of millions of years, establishing a fundamental role for porphyrins in medical diagnosis [1]. Heme also serves as the principal imaging contrast agent for functional magnetic resonance imaging (fMRI). The change from diamagnetic oxyhemoglobin to paramagnetic deoxyhemoglobin can be imaged for interpretation of neural activity based on blood oxygenation [2, 3]. In the past decade, theranostic medical techniques combining imaging and therapy have seen a rapid expansion [4]. Porphyrins and related compounds, with their inherent theranostic optical activity, hold potential for these techniques [5].

Five classes of tetrapyrrole structures are shown in Figure 1A [6]. Porphyrin macrocycles contain of four pyrrole subunits linked together via methine bridges. Reduction of one or two double bonds yields chlorins and bacteriochlorins, respectively. Phthalocyanine and naphthalocyanine contain one or two additional outer cyclohexadiene rings attached to the pyrrole groups, respectively. Typical absorbance spectra of these five tetrapyrroles are shown in Figure 1B. The porphyrin spectrum contains one intense Soret band and multiple Q-bands. For even modest light penetration into biological tissues, excitation of porphyrin Q-bands is required since light with near infrared (NIR) wavelengths can penetrate tissue deeper than shorter wavelength light. However, the absorption of porphyrins at long wavelengths is limited. The other classes of tetrapyrroles provide much higher absorption coefficients in the NIR.

FIGURE 1

Figure 1. (A) Structure and (B) Absorption of typical porphyrins, chlorins, bacteriochlorins, phthalocyanine and naphthalocyanines. Arrows show Q-band absorption (Adapted with permission from Berg et al. [6]).

Porphyrins can be simply solubilized in water or surfactants, administered intravenously and a target area can be irradiated as is performed in traditional photodynamic therapy (PDT) [7]. However, many types of drug carriers and nanoscale designs can be used together with porphyrins for a variety of applications in imaging and therapy. Porphyrins themselves can actively form a building block in carrier systems. Also, with rational design, porphyrin biomaterials can function like stimuli-responsive smart drugs. These materials fit a broad range of diagnostic and therapeutic applications as shown in Figure 2, and will be discussed throughout this review.

FIGURE 2

Figure 2. Examples of porphyrin-based biomaterials (inner circle) and applications (outer circle). (A) Liposomal phthalocyanine delivery [8]; (B) Glycoporphyrin dendrimers [9]; (C) Photodynamic molecular beacons [10]; (D) Porphyrin-phospholipid porphysome. [11]; (E) PpIX-modified mesoporous silica nanoparticle [12]; (F) Pd-porphyrin cross-linked hydrogel [13]; (G) In vivo MRI image of Mn-porphyrin nanoparticles [14]; (H) microPET/CT image of orthotopic PC3 tumor model after injection with ⁶⁴Cu-porphysomes [15]; (I) Fluorescence tracking of macrophages after injection of porphyrin-modified nanoparticles [16]; (J) Human esophageal cancer treated with PDT [17]; (K) Thermal images of tumor-bearing mice with Pc-loaded nanoparticles exposed to a NIR laser [18]; (L) 8 h (a1) and 24 h (a2) radioimaging of melanoma-bearing mice after injection with ¹⁸⁸Re-T_3,4CPP [1]; (M) Acoustic images of a tumor-bearing mouse after injection with porphyrin-shell microbubbles [19]; (N) Image-guided surgery with a porphyrin-PEG cross-linked hydrogel [20]; (O) Phosphorescence images of an implanted Pd-porphyrin hydrogel in mice breathing different oxygen levels [13]; (P) Photoirradiation of bacteria under various photosensitizer conditions [21]; (Q) Photoimmunotherapy concept [22]. All figures used with permission from the indicated references.

Numerous porphyrin-based photosensitizers have received clinical approval or have entered clinical trials, and these have been reviewed extensively in the literature [7, 23–27]. Undesired sunlight photosensitivity, poor light absorption in deep tissues, and off-target damage to other bystander tissues have led to sustained efforts in the development of improved photosensitizers. Porphyrins were first approved clinically for cancer treatment with Photofrin in 1993 for treatment of bladder cancer [7]. Subsequently, chlorins have been increasingly used as photosensitizers due to their enhanced Q-band absorption. Numerous therapeutic commercial formulations have become available for a range of clinical applications, as shown in Table 1 [28–33]. This steady stream of new PDT compounds illustrates the inherent biocompatibility of porphyrins and their efficacy as photosensitizers.

TABLE 1

Table 1. Selected clinical photosensitizers.

The fundamental goal in PDT is to oxidize cellular biomolecules via singlet oxygen, thereby inducing cell damage and death [34]. The principal cytotoxic agent, singlet oxygen (¹O₂), is generated by energy transfer from photosensitizers to molecular oxygen (O₂) [35]. The method for the production of ¹O₂ in tissues requires oxygen, light of an appropriate wavelength, and a photosensitizer. The excitation of the sensitizer is achieved via an absorbed photon transition between the ground state S₀ and a singlet excited state S_n. The lowest excited singlet state of the sensitizer S₁ is from relaxation of the S_n state. The sensitizer triplet state (T₁) occurs following intersystem crossing. The triplet state lifetime is longer than that of the S₁ state and it is the excited triplet that can damage the cell by one of two ways; type I or type II mechanisms [36].

In type I mechanisms, the photosensitizer may directly react with a biological substrate via radical formation. The free radicals or radical ions are usually produced by interaction of the triplet sensitizer with a reducing substrate. Scenarios which will produce radicals include the insertion of oxygen or electron transfer to oxygen, electron or hydrogen abstraction from other substrates, initiation of free radical autoxidation, and back electron transfer relations [37]. In type II processes, the triplet state photosensitizer interacts with ground state molecular oxygen (³O₂) first to produce highly reactive ¹O₂, which proceeds to attack cellular targets. This specificity allows examination of the potential roles of ¹O₂ in cellular systems. Type II processes are generally considered most relevant to current PDT practice.

Applications of Metalloporphyrins

Due to its unique structure comprised of delocalized π-electrons within a tetrapyrollic skeleton, porphyrins and related molecules not only are intensely colorful, but can also chelate a vast number of metal ions. Extensive inorganic coordination chemistry research involving porphyrins has shown that dozens of elements from the periodic table can be chelated into the center of the macrocycle (e.g., Li, Be, Na, Mg, Al, K, Ti, Mn, Cu, Co, Fe, Pt, Tm, Yb, and Lu) [1]. Investigations into metalloporphyrins for diverse catalytic functions have been explored extensively [38–40]. Different metalloporphyrins are capable of providing imaging contrast for near infrared (NIR) fluorescence, magnetic resonance imaging (MRI), X-ray computed tomography (CT), and emerging modalities like photoacoustic imaging. Because of their potential applications in these diagnostic techniques, the study of metalloporphyrins remains active. Different metal selection allows for control of the photochemical and electrochemical properties.

Among metalloporphyrin derivatives, palladium and platinum-chelated porphyrins are attractive photosensitizers for their high singlet oxygen yields and their capacity for oxygen sensing [41, 42]. Due to the sensitivity of their phosphorescence to molecular oxygen, Pd(II)- and Pt(II)- porphyrins have become important probes for in vitro [43, 44] and in vivo oxygen detection [45–47]. Moreover, their long-lived NIR phosphorescence lifetimes can help reduce background from shorter lifetime auto-fluorescence effects from surrounding tissue. In 1995, Vinogradov et al. found several Pd-chelated porphyrins which showed high sensitivity to oxygen concentration changes [48]. Subsequently, numerous formulations of phosphorescent probes have been developed involving copolymers [49], nanoparticles [50–52], dendrimers [53–55], and hydrogels [13, 56].

Besides oxygen sensing, Pd(II)- and Pt(II)-porphyrins are effective PDT agents. Cheng et al. embedded Pd-meso-tetra (4-carboxylphenyl) porphyrin onto the nano-channel surface of mesoporous silica nanoparticles through amido bonds [57]. After incubation with MDA-MB-231 cells, there was significant damage shown in cell morphology following a brief irradiation. Later, similarly structured mesoporous silica nanoparticles were obtained by further surface modification with PEG and RGD molecules [58]. Both the PEG- and RGD- modified nanoparticles showed good efficiency in cellular uptake, bright luminescence, and good PDT efficacy following incubation with cancer cells.

Another unique metal for porphyrin chelation is copper, which has a high chelation affinity for the macrocycle, even in mild aqueous reaction conditions. As shown in Figure 3, Shi et al. reported ⁶⁴Cu porphyrin radiolabeling in a multifunctional chelator complex [59]. This complex served as an optical imaging probe, a PDT agent, and a PET imaging probe. A pharmacokinetic-modifying linker was used to enhance the water solubility of the porphyrin-peptide-folate (PPF) probe. Folate is a well-established metabolite that can be used to effectively improve cancer targeting specificity [60]. Mice were first injected with ⁶⁴Cu-labeled PPF and analysis showed the stability of the ⁶⁴Cu labeled metalloporphyrin complex. Micro CT and micro PET imaging were then performed 4 and 24 h post-injection and the tumor was easily identified with PET.

FIGURE 3

Figure 3. Pyro-pharmacokinetic modifying linker (peptide sequence)-folate (PPF) structure design (Adapted with permission from Shi et al. [59]).

Zhang et al. recently reported medical imaging applications of naphthalocyanines and spectrally-shifted metallonaphthalocyanines. Dyes were encapsulated with pluronic F127 by drop wise addition of the naphthalocyanines (Nc) into a 10% Pluronic F127 solution to form a micelle structure of nanoformulated naphthalocyanine, termed nanonaps [61]. After removal of excess surfactant, a dye to surfactant molar ratio of greater than 3 was determined. Nanonaps exhibited stability in the harsh conditions of the stomach and intestine and the particles were fully excreted in feces. Nanonaps exhibited strong photoacoustic signal generation capabilities. In vivo, the photoacoustic signal could penetrate about 2.4 cm deep though tissue and the movement of nanonaps could clearly be visualized in the intestine. Nanonaps could also be labeled with ⁶⁴Cu for complementary whole-body PET imaging.

Magnetic metals have also successfully been chelated in porphyrins, offering MRI contrast enhancing capabilities. Mn(III) can be used for medical imaging, but can be toxic when used in high concentrations. However, porphyrins can stably chelate the metal to inhibit unwanted toxicity from large doses [62]. Cheng et al. reported complementary chemical strategies to overcome the limitations of Mn-porphyrin and enhance biocompatibility, pharmacokinetics, and high-field T₁ MRI properties [63]. The first strategy was based on Mn meso-tetra (4-sulfonatophenyl) porphyrin, which is capable of providing contrast at high magnetic field strengths, unlike common Gd contrast agents. They found that by varying the size of these Mn-porphyrins they could tune the speed of clearance from the body. Two similar derivatives of the Mn meso-tetra (4-sulfonatophenyl) porphyrin were tested following intravenous injection in mice. They found that the smaller and polar type of Mn-porphyrin accumulated in the kidneys and bladder within 10 min, validated by whole body MRI. The signal disappeared after 24 h post-injection and clearance was confirmed by urine analysis. The renal clearance profile of the larger Mn-porphyrin was significantly slower, demonstrating the ability to tune pharmacokinetics to fit different applications.

Photodynamic Molecular Beacons

It is possible to build additional layers of control onto PDT photosensitizers, based on activation following recognition of specific biomolecules or biological conditions. These so-called activatable photosensitizers are a new class of photosensitizers which add a layer of complexity over standard photosensitizers, but also offer opportunity for target-tissue specific imaging and therapy [64]. With appropriate design, a photosensitizer that moves to an excited state following photon absorption can be quenched at several different stages prior to generation of singlet oxygen (Figure 4). This photosensitizer deactivation itself can be modulated by various biomolecules such as proteases or nucleic acids, resulting in photosensitizers that are, ideally, only active in target tissues where those targets are present.

FIGURE 4

Figure 4. Possible pathways for rational deactivation of an excited state photosensitizer. Simplified singlet oxygen generating diagram with energy levels shown in black and the typical pathway of singlet oxygen generation in red (Adapted with permission from Lovell et al. [64]).

Nucleic-acid Activatable Photosensitizers

Molecular beacons have become archetypal molecular probes and are powerful tools for detecting nucleic acids with single base precision [65]. Traditional molecular beacons are nucleic acid-based sensors consisting of a single stranded oligonucleotide probe with a loop and stem structure. At each terminus is a dye or quencher that are inactive when proximal. When the target is present, the probe loop opens up to form a two-stranded duplex, resulting in separation of the fluorophore and quencher and an increased signal.

The quencher is responsible for energy capture and transfer from the excited fluorophore [66]. A commonly used quencher is 4-(4-dimethylaminophenylazo) benzoic acid (dabcyl). Dabcyl is a hydrophobic molecule and also a universal quencher for many fluorophores [67]. However, quenching efficiency decreases for dyes emitting longer wavelengths, although alternative quenchers such as gold nanoparticles can be used in certain cases [68]. FRET efficiency can be used to predict the response of photodynamic molecular beacons [69]. Enzymes, nucleic acids, chemical environments and even other photosensitizers are able to activate photodynamic molecular beacons [64, 70, 71].

Nucleic-acid based activatable photosensitizers follow the same design principles as classic molecular beacons except that a photosensitizer is used in lieu of a fluorophore. This principle was first shown in 2008 by Chen et al., who reported a photodynamic molecular beacon (PMB) with tumor specific mRNA-triggered control of singlet oxygen production [72]. The photosensitizer remained silenced in the absence of the nucleic acid target. However, photodynamic activity was restored in the presence of a complementary mRNA sequence.

Lovell et al. enhanced singlet oxygen quenching in the beacon off state by using a so-called linear superquencher consisting of multiple quenching moieties [73]. The construct, with three quenchers, achieved more than 300 fold quenching in the off state. In the presence of targeted DNA in the system, the beacon opened and singlet oxygen production was restored. Due to the hydrophobic structure, this same beacon could partition into lipid-based nanoparticles [74]. Unexpected aggregation was observed in the presence of the target nucleic acid, indicating that photodynamic molecular beacon opening can induce physical perturbations in nanoparticle systems.

Nesterova et al. designed a phthalocyanine (Pc) dimerization based molecular beacon system using phthalocyanines [75]. As shown in Figure 5, the design involved a non-fluorescent H-dimer in the molecular beacon off state. The presence of a complementary DNA sequence caused the formation of a duplex, thereby disrupting the quenching mechanism and restoring fluorescence. This experiment was done with respect to the oligonucleotide chain length. They found that longer oligonucleotide sequences could better restore fluorescence emission. The H-dimer based molecular beacon (Pc2) produced 98% quenching efficiency with a signal to background ratio of 59.

FIGURE 5

Figure 5. Schematic representation of a dimer based photodynamic molecular beacon is shown on the left and the structure of Pc1 and Pc2 are shown on the right (Adapted with permission from Nesterova et al. [75]).

Enzyme Activatable Photosensitizers

Enzyme activated photosensitizers are typically quenched until specific enzymatic activity liberates the photosensitizer from a particular quenching environment. In some cases the photosensitizer is tethered via a peptide linker to a quencher, or sometimes the photosensitizer is grafted with peptide linkages onto a polymeric backbone [76, 77]. Whereas most enzymes used for activation have been proteases, other enzymes such as lipases can also be used with appropriately designed photosensitizers [78].

In 2004, Chen et al. reported a photosensitizing beacon design made with a disease-specific linker, a photosensitizer, and a singlet oxygen quencher/scavenger (Figure 6) [79]. In their design, the photosensitizer and singlet oxygen quencher were linked to two ends of a peptide sequence. This design allowed the photosensitization to remain quenched in the absence of the specific target molecule [79]. They chose a well-established peptide sequence, cleavable by caspase-3, as the substrate [80]. Pyropheophorbide α (pyro) was used as a photosensitizer. The quencher carotenoid was selected to quench and scavenge singlet oxygen [81]. The quencher efficiently decreased singlet oxygen production. The pyro-peptide-carotenoid (PPC) was cleaved when caspase-3 was introduced, resulting in increased singlet oxygen signal. This approach has also been extended to photodynamic beacons that both induce and sense apoptosis [82].

FIGURE 6

Figure 6. (A) Principle of singlet oxygen scavenging and activation (B) structure of a caspase-3 activatable pyro-peptide-carotenoid photodynamic beacon (Adapted with permission from Chen et al. [79]).

Chen et al. later modified their beacon design using a zipper molecular beacon (ZMB) held together by electrostatic forces of positive and negative peptide residues [83]. They found that enhanced quenching efficiency in the ZMB was the result of both improved fluorescence resonance energy transfer (FRET) effect, and the ground state complex quenching caused by annealing of the dye and quencher through the electrostatic attraction of the zipper arms. A central protease cleavage site allowed for enzyme activation, and the ZMB produced a high signal/background ratio after activation. The ZMB also had the ability to increase the resolution of activated probes and increase the contrast between intact and activated beacons during a cellular uptake experiment.

Nano- and Micro-structured Porphyrin Agents

The rise of nanomedical engineering has generated interest and improved methodology in designing effective nanoparticulate agents [84]. Porphyrin and its derivatives have been tested in many biological applications along with liposomal delivery, conjugation with biocompatible polymers, or other nanoparticles. These nanomaterials can be functionalized with specific ligands that deliver porphyrins to target areas. Tunable size allows them to effectively reach tumor cells easily through enhanced uptake or direct penetration through cell membranes. These materials work as multifunctional platforms with diagnostic and therapeutic abilities in vitro and in vivo [85].

Porphyrin Dendrimers

Dendrimers have highly branched three-dimensional architecture with properties that can be precisely controlled and hold promise as nanocarriers [86, 87]. In 1993, dendrimer porphyrins were reported by Jin et al. [88]. The structure of dendrimers shows three critical architecture domains: a multivalent surface, interior shells, and a core. The high density of functional groups on the dendrimer surface makes them a versatile nano-scaffold. The interior core can exhibit host-guest interaction, which mimics micelle structure when host and guest are hydrophobic and hydrophilic molecules respectively [86]. Porphyrin photosensitizers, which are usually hydrophobic, can be attached to the branches or encapsulated in the core [89]. In this way, porphyrins can be made to mimic natural heme-containing proteins. Interestingly, organic reactive groups around porphyrins can be exchanged during the synthesis process, with enough attached in the periphery of dendrimer to create light-harvesting materials [90].

Porphyrin-Containing Liposomes

Liposomes have been widely used as porphyrin delivery agents [91]. These spherical nanoparticles possess a hollow core that isolates an interior aqueous environment from an exterior one. Liposomes can encapsulate both hydrophobic and hydrophilic materials. Besides disease specific targeting ligands, liposome surfaces have been modified with many organic and inorganic compounds to better accomplish the goal of reduced toxicity and increased therapeutic index [92]. Enhancing the biocompatibility or biodegradability of liposomes can be accomplished by a variety of techniques. Modifying lipid composition, surface charge, in vivo or shelf stability, and permeability are just some routes by which this has been achieved [93]. Then, based on the desired properties for each application, the appropriate formulation can be determined. Liposomes injected intravenously are generally taken into the mononuclear phagocytic system. Short blood circulation time generally will decrease delivery efficiency. To overcome this phenomenon, surface modifications like coating with polyethylene glycol (PEG) can help control the clearance time [94]. PEGylated liposomes can be designed for conjugation with antibodies for the combination of long-circulation and targeted delivery [95].

Porphyrin-Phospholipid Compounds

In 2005, porphyrins were incorporated into polymersome nanovesicles [96]. Later, in 2011 it was determined that by covalently conjugating a porphyrin on a phospholipid side chain, the porphyrin-phospholipid could self-assemble into nanovesicles termed porphysomes, forming a pure porphyrin-bilayer [11]. Porphysomes can be used for diverse biophotonic applications including photothermal therapy and photoacoustic imaging. Porphyrin-phospholipid micelles are also promising theranostic agents [97]. In recent years there has been a push to improve and explore more clinically relevant applications of porphysome technology [98]. Diagnosis and treatment for specific types of cancer has especially driven innovation [99–103].

Because metalloporphyrins possess multifunctional imaging abilities, metallo-porphysomes have been successfully developed for different diagnostic techniques. In 2012, Tam et al. successfully formed stable surface enhanced Raman scattering (SERS) probes by embedding gold nanoparticles into Mn-pyro-lipid porphysomes [104], showing the potential of porphysomes as metal-nanoparticle carriers. Recently, MacDonald et al. used a similar method to generate Mn-pyro-lipid porphysomes for use as MRI contrast agents [105]. The porphyrin lipid was chelated with Mn(II) as shown in Figure 7. The MRI signal from Mn-pyro-lipid porphysomes was comparable to Gd-DTPA, a clinical MRI contrast agent.

FIGURE 7

Figure 7. Schematic showing the post chelation process of Mn ion into the pyro-lipid. (Adapted with permission from MacDonald et al. [105]).

Recently, ⁶⁴Cu porphysomes have been demonstrated for use as in vivo PET imaging agents. In 2012, Liu et al. chose prostate cancer as a platform to test the PET diagnostic ability of ⁶⁴Cu-porphysomes [106] after labeling them as shown in Figure 8A. 24 h post injection, ⁶⁴Cu porphysomes accumulated within prostate tumors and showed a bright PET signal (Figure 8B). They used similarly structured ⁶⁴Cu-porphysomes for further prostate tumor treatment research [15]. After intravenous injection in vivo, the results demonstrated high uptake efficiency and high specificity to PC3 tumors (Figure 8C). Results of ⁶⁴Cu chelated porphysomes point toward potential clinical translation possibilities.

FIGURE 8

Figure 8. (A) Schematic figure showing the process of chelating ⁶⁴Cu ion into porphysomes; (B) MicroPET/CT images of coronal single slices through orthotopic PC3 tumor at 24 h after intravenous injection ⁶⁴Cu-porphysomes; (C) 3D MicroPET/CT images (blue arrow, distal femur metastases, white arrow, proximal tibia metastases) (Adapted with permission from Liu et al. [15, 106]).

As opposed to modifications on the porphyrin macrocycle, there are several other modifications that can induce enhanced liposome release. Methods that have already been developed include pH triggering [107, 108], biodegradability [109, 110], and thermal sensitivity [111]. These techniques can also be applied to modified porphysomes. In 2012, specific enzyme-biodegradable porphysomes were made by Lovell et al. [112]. By performing side-chain modifications, two similarly structured porphysomes showed significant biodegradable differences. Sn-1 regioisomeric porphysomes remained intact in the liver and spleen, while sn-2 regioisomers showed dramatic degradation. This result illustrates the possibility for controlled porphysome degradation, and the potential for release of contents in specific organs.

More recently, folic acid modified porphysomes were developed by Jin et al. This nanosystem embedded quenched photosensitizers in intact porphysomes and triggered disruption in target cancer cells for PDT under light irradiation [113]. According to the results, a notable difference was observed between cellular uptake efficiency of the nanoparticle with and without the folate acid ligand. After laser treatment, the tumor tissue with folic acid targeted porphysomes was totally destroyed with no reappearance within 14 days.

Porphyrin liposomes can also be used for light-triggered drug delivery applications [114]. Devinyl hexyloxyethy-pyropheophorbide (HPPH)-conjugated phospholipids were incorporated into nanovesicles that could be permeabilized by NIR-light. Various cargos could be released from the liposomes during NIR irradiation. During liposome formulation, doxorubicin was successfully loaded and released from these nanovesicles, which were shown to re-seal with an intact membrane when no longer exposed to NIR light. These nanovesicles with controlled drug release properties successfully cured nude mice with KB tumors and exhibited no appearance of regrowth within 90 days. Light-triggered permeabilization of microparticles has also been demonstrated [115].

Recently, a porphyrin-phospholipid-coated upconversion nanoparticle (UCNP) was developed by Rieffel et al. The UCNP (core-shell of NaYbF₄:Tm-NaYF₄) was surface modified with PEG- and porphyrin-phospholipid, and also was incubated with ⁶⁴Cu, showing high stability in aqueous system. This nanoparticle probe was shown to enhance signal or contrast in six different imaging techniques including UC imaging, fluorescence, photo acoustic imaging, PET, CT and Cerenkov imaging. The phantom and in vivo data both provide high quality images with this UCNP probe [116].

In addition to the nano-sized spherical porphysomes mentioned above, micro-sized and other structured porphyrin-lipid complexes have been developed. One example is the nanodisc formed by ApoA-1 and porphyrin-lipid [117], as shown in Figure 9.

FIGURE 9

Figure 9. Schematic of the self-assembling process resulting in porphysome nanodics (Adapted with permission from Ng et al. [117]).

After forming intact nanodiscs, fluorescence and singlet-oxygen generation were fully quenched. Following enzymatic degradation, the fluorescence and singlet oxygen generation recovered due to disruption of the structure. Another example is porphyrin shell “porshe” microbubbles (Figure 10) [19]. These micromaterials were generated by mixing porphyrin-lipid, phospholipid, polyoxyethylene-40 stearate, phosphate-buffered saline (PBS), and fluorinated gasses together through a mechanical agitation method. Porshe microbubbles were stabilized around 2.7 μm, creating a large-volume empty cavity. These microbubbles are stiffer than commercial microbubble agents and exhibited photoacoustic and ultrasound signals both in vitro and in vivo. Besides photoacoustic and ultrasound imaging abilities, microbubbles also have potential applications working as drug or gene delivery carriers.

FIGURE 10

Figure 10. (A) Schematic of the structure of microbubble (B) Photo of microbubbles solutions in room temperature (Adapted with permission from Huynh [19]).

Mesoporous Silica-Porphyrin Nanoparticles

Mesoporous silica nanoparticles are appealing for biomedical applications due to their uniform porosity, ease of functionalization, and biocompatibility [118–120]. Due to their monodispersity, high surface area, and tunable pore size and diameter [120, 121], they are being researched as nanocarriers for fluorescence [122], MRI [123–125], drug delivery [126], and PDT [12, 127, 128] applications. The PDT efficiency of porphyrins is increased by overcoming limitations such as biotoxicity, low solubility in water, and non-specific toxicity following formulation with mesoporous silica nanoparticles.

Research into porphyrin photosensitizers conjugated with mesoporous silica nanoparticles has expanded tremendously in recent years. Many strategies have been employed, one of which is self-assembly of silica-porphyrin conjugates directly [129–133]. These silica-porphyrin molecules can be bonded to other chemical linkers, stimulating the formation of mesoporous nanoparticles. The role of porphyrin in mesoporous silica nanoparticles is to impart imaging capability, act as a photosensitizer, and to chelate metals. In 2010, gold nanorods were encapsulated in the core of porphyrin conjugated mesoporous silica nanoparticles [130]. Besides singlet oxygen generation, these nanoscale materials showed high-contrast two-photon images after being used to treat a MDA-MB-231 human breast adenocarcinoma cell line. In a subsequent study, silicon phthalocyanine molecules were conjugated with mesoporous silica nanoparticles (Pc4SNP) and used for PDT. After light irradiation, A375 and B16F10 melanoma cells incubated with Pc4SNP for 24 h showed dramatically decreased viability. These nanoparticles were found to be partially internalized into mitochondria and lysosomes [134].

Porphyrins can also be embedded into mesoporous silica nanoparticles. In 2009, a zinc phthalocyanine-loaded mesoporous silica shell was developed by Qian et al. This porphyrin-mesoporous silica nanoparticle was active in the NIR, and was shown to kill more than 80% of murine bladder cancer cells by PDT [135]. In 2012, another method of using zinc phthalocyanine loaded into silica-shell nanoparticles was shown by Tu et al. [136]. Cell penetration efficiency was increased by co-coating with PEG and polyethyleneimine. Moreover, these silica nanoparticles loaded with zinc phthalocyanine showed bright NIR signals and were implemented as an effective anti-tumor treatment. A new conjugation method was attained through allylisocyanate [133]. The internalization of these nanoparticles in MCF-7 breast cancer cells was observed by confocal microscope imaging, and an efficient PDT response from these porphyrin-silica nanoparticles was demonstrated following laser irradiation.

Porphyrin-conjugated mesoporous silica nanoparticles were recently considered as dual-function drug carriers for delivery to a specific target area. After being conjugated with porphyrin and loaded with anticancer drugs, enhanced anticancer therapy was achieved. In 2011, Wang et al. introduced a dual-mode therapeutic multifunctional nanocarrier to deliver doxorubicin to cancer cells [137]. In this study, hollow cubic core and mesoporous shell nanoparticles were made by surface etching of the shell molecules. Isothiocyanate and hematoporphyrin were incorporated into the nanoparticle walls through covalent bonds, acting as fluorescence probes. Doxorubicin molecules were encapsulated into the pores of the nanoparticle. After being incubated with MCF-7 cells, the doxorubicin-nanocage system demonstrated much lower cell viability compared to doxorubicin and nanocages alone. These results indicate this dual-functional nanoparticle can provide enhanced anticancer therapeutic ability and complementary imaging capacity.

Porphyrin Hydrogels

Hydrogels are three-dimensional networks of hydrophilic polymers capable of containing a large amount of water. Hydrogels have a range of biomedical and pharmaceutical applications, such as in tissue engineering [138–140], drug delivery [141, 142], PDT [143], and photodynamic antimicrobial chemotherapy [144, 145].

Photodynamic antimicrobial chemotherapy (PACT) is a form of PDT that uses light sensitizing drugs to kill microorganisms. Because of the flexibility of hydrogels during the formation process, they can be molded to different shapes appropriate for different clinical conditions, usually around a surgical wound. After surgery for example, the oxygen concentrations around the wound and subcutaneous conditions could be monitored through clinical imaging techniques. The porphyrin photosensitizers can also generate singlet oxygen causing damage to microorganisms, attaining the PACT goal.

Porphyrins and phthalocyanines have been explored as agents to attenuate microbial growth for decades [146]. In 2009, Donnelly et al. used a cross-linked poly (vinyl alcohol) hydrogel loaded with two photosensitizers, methylene blue and meso-tetra (N-methyl-4-pyridyl) porphine tetra tosylate, for antibacterial infection treatment [144]. In the same year, a porphyrin surface modified hydrogel was developed by Parsons et al. for the prevention of intraocular lens-associated infectious endophthalmitis [147]. Cationic tetrakis (4-N-methylpyridyl) porphyrin interacted electrostatically with anionic HEMA (2-(hydroxyethyl) methacrylate) and methacrylic acid and a promising antimicrobial reduction in adherence of S. epidermidis was shown.

Due to the high biocompatibility and stability of hydrogels, they can stay in a subcutaneous position around wounds for a long period without any side effects. The native imaging abilities of porphyrins provide a non-invasive way to monitor implanted hydrogel within tissues. Lovell et al. cross-linked meso-tetrakis (4-carboxyphenyl) porphine with diamine-functionalized PEGs [20]. After implantation in vivo, the hydrogel showed a detectable fluorescent signal in the subcutaneous position for 2 months and there were no side effects during or after removing the hydrogel. In 2014, a thermosensitive porphyrin-incorporated polycaprolactone (PCL)-PEG hydrogel was developed [148]. This POR-PCL-PEG hydrogel maintained a liquid sol state at room temperature, but after subcutaneous injection, the body temperature stimulated the liquid formation of a sol gel, which transformed to a solid hydrogel within 1 day. Within 9 days, the hydrogel degraded and most of it remained close to the injected position. A very small amount migrated to other organs but no damage signs were apparent in these organs, demonstrating excellent biocompatibility.

Other Emerging Porphyrin Applications

Photothermal therapy (PTT) is another type of anti-cancer treatment being explored. Being similar to PDT with respect to light delivery to biological tissues, a photosensitizer can be used to enhance heating and to ablate tumors. To achieve a higher therapeutic efficiency, researchers have also combined PDT and PTT agents. In 2011, Jang et al. combined Al (III) phthalocyanine chloride tetrasulfonic acid (AlPcS₄) with gold nanorods. By excitation with a 810 nm laser, the temperature around the tumor tissue increased to 65°C [149]. Phthalocyanines and metallo-naphthalocyanines have successfully been delivered in vivo through polymerization or combination with common nano-carriers [18, 150, 151]. After injection into mice, all of the subjects showed large temperature increases with laser stimulation, and demonstrated high levels of anti-tumor efficacy. In 2013, Jin et al. used porphysomes as PTT agents. After exposure to the laser for only 85 s, the temperature around tumors reached more than 60°C. Also, compared to the commercial PDT agent Photofrin, these PTT agents showed high therapeutic ability under both acute hypoxic and hyperoxic conditions, while Photofrin could only cure the tumors under hyperoxic conditions [101].

Two-photon imaging uses photons with half the energy of the corresponding one-photon transition and due to their intrinsic imaging ability, many porphyrin agents have been explored as two-photon probes [152]. Porphyrin dimers present unique imaging properties [153–155], as do electrostatic assemblies comprised of porphyrin and polymers [156]. In 2010, Poon et al. synthesized an amphiphilic ruthenium (II)-polypyridl porphyrin complex. Besides the higher cell uptake efficiency after incubation with human nasopharyngeal carcinoma HK-1 cells, this Ru-porphyrin complex also demonstrated high red fluorescence intensity after excitation with a 800 nm laser [157]. In the same year, Sakadzic et al. used Pd-porphyrins encapsulated in poly (arylglycine) dendrimers as a two-photon-enhanced phosphorescent probe for detecting oxygen levels. The probes showed a strong phosphorescence signal in microvasculature up to 250 μm deep below the cortical surface, overcoming the low two-photon signals seen when using other oxygen phosphorescence probes [45]. Porphyrin nanoparticles have also been used for two-photon applications [158].

Targeted PDT involving porphyrins has been explored extensively and continues to attract interest. Conjugation of photosensitizers to antibodies has been explored for decades for photoimmunotherapy (PIT) [159]. As opposed to traditional passive targeting methods, photosensitizers can actively target diseased tissues through covalent binding with antibodies or antibody fragments. The antibodies chosen to decorate delivery vehicles have the ability to bind with cancer-tissue associated antigens. MAbs usually play the role of blocking specific receptor signaling pathways in cells, or as vectors to deliver porphyrins into target cancer cells [160]. Various types of antibodies have been used including intact IgG, and single chain fragments (scFV) successfully bind with porphyrin-based photosensitizers. This formulation of photodynamic agents has progressed well in treatment of diseases such as ovarian cancer [160], human colon carcinoma [161], L-M fibroblasts [162], and human breast carcinoma [162]. In 1983, Mew et al. combined hematoporphyrin with anti-M-1 to treat DBA/2J myosarcoma M-1 in mice. Their conjugates killed 95% of tumor cells in vitro and restrained tumor growth after injection into mice [163]. Later, Goff et al. used chlorin derivative, CMA, conjugated with anti-ovarian carcinoma monoclonal antibody OC125. After incubation with cells for 1 h and irradiation with a 654 nm laser, the PIT agent shown obvious selectivity to ovarian cells compared to other non-ovarian cells [164]. Furthermore, in 2005, Hudson et al. utilized two porphyrin isothiocyanates (one is neutral and one is positive charged) for facile conjugation with internalizing MAb FSP 77 and 17.1A, and non-internalizing MAb 35A7. Based on their results, all the conjugates demonstrated increased efficiency compared to free photosensitizers with the internalizing conjugates performing better than non-internalizing variants. Also, comparing to the two photosensitizers, the cationic agent shown shorter serum half-life and a high loading ratio [165]. In 2011, conjugation of trastuzumab or panitumumab (which are against human epidermal growth factor HER1 and HER2) with the phthalocyanine-based dye IR700 was performed. Each mAb combined with approximately three dyes. Trastuzumab-IR700 fluorescence signals were detected on the cell surface and internally after incubation with 3T3-HER2 cells for 1 and 6 h, respectively, and induced cellular death after laser irradiation. The same result was observed after incubating Panitumumab-IR700 with HER1-positive A431 cells. Also, in vitro data showed phototoxicity of mAb-IR700 conjugations only to the target cells. After injection into mice, both mAb-IR700 conjugations demonstrated target-specific accumulation; and with treatment 1 day post-injection, both conjugations led to significant tumor shrinkage [166]. During the treatment of A431 cancer with Panitumumab-IR700, Mitsunaga et al. found repeated exposure to light of the target tissue area will lead to enhanced therapeutic efficiency [167]. Recently Kobayashi et al. have been applying this approach to various mouse models of cancer including MDAMB468-luc cells and disseminated peritoneal ovarian cancer have successfully been treated with this approach [168–170]. With advances in antibody production techniques coupled with development of porphyrin-based photosensitizer synthesis, clinical translation of PIT is possible.

Besides PIT, vascular targeted PDT is another approach for anti-cancer therapy [171]. This is accomplished through attacking vascular tissue around tumor sites to generate localized necrosis. The common method for anti-vascular therapy is based on damaging blood vessels, inhibiting formation of de novo neovascularization, and stopping blood flow [172]. In 2004, Brandis et al. developed a hydrophilic bateriochlorophyll derivative compound of Pd-bacteriopheophorbide (Tookad), which has been used in clinical trials as an anti-vascular agent. Differing from other anti-vascular agents, their molecules showed low aqueous aggregation and high affinity to serum proteins, which could extend the circulation time of these agents and bring them to the vasculature of important target organs [173]. In 2014, Reddy et al. used Photofrin combined with iron oxide crystals and polyethylene glycol to form a multifunctional platform that could shrink orthotopic gliomas in rats [174].

Conclusion

As clinical agents for PDT, porphyrins occupy a central niche in photomedicine. A variety of metalloporphyrin derivatives have been synthesized as probes for diagnostic techniques, such as fluorescence imaging, MRI, PET, and CT. Photodynamic molecular beacons are promising constructs to enhance localized activation of porphyrins for PDT and imaging. Modified liposomes, dendrimers and other nanoparticles serve as carriers to deliver porphyrins to the target tissues. Recent porphyrin constructs have begun to be used in multifunctional nano- or micro-carriers, which hold potential to deliver drugs to target tissues with higher efficiency. Porphyrins and related macrocycles provide a large range of possibilities to address almost any diagnostic and therapeutic challenge. More work is still needed to advance recently emerging porphyrin constructs to the clinical stage to fulfill their potential.

Conflict of Interest Statement

The authors declare that the research was conducted in the absence of any commercial or financial relationships that could be construed as a potential conflict of interest.

Acknowledgments

This work was made possible with support from the National Institutes of Health (R01EB017270 and DP5OD017898).

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