cancer, mitochondria-targeted photosensitizer, nanoparticles, photodynamic therapy
Photodynamic therapy (PDT) is a novel and promising treatment for cancer treatment, which involves the administration of photosensitizers coupled with a specific wavelength of laser irradiation. In the presence of oxygen, the PDT with particular photosensitizer causes significant formation of singlet oxygen as well as other reactive oxygen species (ROS), which produce severe peroxidative reaction as a major contribution to light-induced cell damage and death. To achieve the best efficacy of PDT, an ideal photosensitizer obliges good tissue penetration, low dark toxicity (effect of photosensitizer alone) and high extinction coefficient. In addition, subcellular distribution of photosensitizers appears to be critically involved in the potency of PDT [1]. Recently, the mitochondrion has been considered as a novel pharmacological target for clinical application including cancer therapy due to its crucial role involved in arbitrating cell apoptosis. Mitochondrial dysfunction leads not only to the interruption of ATP supply but also to the activation of mitochondrial dysfunction-mediated apoptotic pathway. Key mitochondrial mechanism involved is the opening of the mitochondrial permeability transition pore (MPTP), which results in mitochondrial membrane potential (Δψm) depolarization, mitochondrial swelling and release of mitochondrial apoptotic lethal proteins to the cytosol. Subsequently, downstream caspases dependent or independent nuclear proteases are activated to cleave nuclear DNA to small fragments. Intriguingly, mitochondria-associated apoptotic mechanisms, particularly the opening of the MPTP and the release of mitochondrial lethal proteins can be initiated and augmented by mitochondrial ROS (mROS) formation as well as mitochondrial free calcium (mCa2+) overload [2-8]. Thus, PDT with an ideal photosensitizer that is able to localize in the mitochondria may significant promote the generation of mROS and then mROS-dependent mCa2+ elevation. These two PDT-induced pathological conditions may then interact together to achieve a vicious augmentation of mitochondrial dysfunction and to ensure a potent and successful cell apoptosis for a high efficacy of PDT for tumor eradication.
The high photosensitizing character of nano-semiconductor QDs provides great therapeutic potential in cancer therapy [9,10]. Using laser scanning confocal microscopy we demonstrated QDs localized into the mitochondria. Upon visible light coupled PDE of QDs, mROS-mediated apoptosis was observed. The mitochondrial protector, melatonin, and the mitochondria-targeted antioxidant MitoQ significantly inhibited visible light coupled PDE of QDs-induced apoptosis [11]. Similarly, carbon nanoparticle fullerenes (C60) possess also unique photosensitizing character. Recent chemical modifications on the C60 sphere including tris-malonic acid fullerene (C3) increases significantly its solubility in water and hence its application in disease-based nano-biomedical science [12,13]. PDE of C3 (100 nM) coupled with 488 nm laser induces significant mROS formation and Δψm depolarization which causes marked fission and swelling of mitochondria (Figure 1). Mitochondrial hot spots due to significant mROS formation caused significant loss of TMRM indicating depolarized Δψm [14]. PDE of visible light coupled mitochondria-targeted nano photosensitizers via enhancing mROS-mediated mitochondrial stress leading to enhanced apoptosis or necrosis. Thus, these nanoparticle-coupled photodynamic therapy may serve as a potential maneuver for clinical treatment of tumors and cancer in the CNS including glioma and astrocytoma.
Figure 1. PDE of 488 nm laser coupled C3-induced mROS “hot spots” and Mito Q-induced “cold spots”. A) In the absence of Mito Q. B) In the presence of MitoQ (100 nM). PDE of C3 (100 μM) was coupled with 60 s of 488 nm laser irradiation. Aa and Ba, DCF images; Ab and Bb, TMRM image; Ac and Bc merged image of DCF and TMRM. Bar, 5 μm.
The authors would like to thank the technical support provided from Microscopy Core Laboratory, Chang Gung Memorial Hospital, Linkou, Taiwan, and Microscopy Center at Chang Gung University, Tao-Yuan, Taiwan. This work was supported by Grants MOST 106-2320-B-182-001 and MOST 107-2320-B-182-018 (to Jou); MOST 102-2314-B-182A-061 and MOST 103-2314-B-182A-024-MY3 (to Peng) from the Ministry of Science and Technology, Taiwan.
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