Fluorescence photodetection (PD) and photodynamic therapy (PDT) are techniques currently under clinical assessment for both visualization and local destruction of malignant tumours and premalignant lesions. One drawback of these methods found with some photosensitizers is a more or less long-term cutaneous photosensitivity (Wagnières et al, 1998;Dougherty et al, 1990). A more recent strategy for administering photosensitizers involves the application of 5-aminolaevulinic acid (ALA) in order to stimulate the formation of protoporphyrin IX (PpIX) in situ. The exogenous ALA bypasses the negative feedback control from haem to ALA synthase that catalyses the condensation of glycine and succinyl-coenzyme A (CoA). Given in excess, exogenous ALA thus can result in a temporary accumulation of PpIX, in particular, in cells with higher metabolic turnover. Since PPIX has fairly good photosensitizing properties (Cox et al, 1982;Kennedy et al, 1990) proposed ALA as a possible photodynamic agent. Following this pioneering work, this treatment modality has been widely studied for various cancers (Kennedy et al, 1992;Peng et al, 1992;Svanberg et al, 1994).As well as for the PDT of malignant or premalignant lesions, ALA-induced PpIX is now being used for the detection of such lesions. This technique has been shown to work, among other applications, in urology, where easy instillation in the bladder, combined with the fact that this organ is readily accessible endoscopically, makes it an ideal object. Alongside classical techniques such as cytology or white light examination, fluorescence PD by ALA-induced PpIX provides some advantages (Leveckis et al, 1994;Kriegmair et al, 1996;Jichlinski et al, 1997). This inspection modality allows an exact mapping which pinpoints, with a high level of sensitivity and specificity, the locations of carcinoma in situ (CIS) as well as early stages of cancer-like dysplasias, which are normally difficult to recognize under white light examination.However, when using topically instilled ALA for the PDT of CIS and precancerous lesions, this modality appears to be limited by the amount of ALA that enter the target cells or by the tissue penetration and the distribution of the resulting PpIX in the targeted tissue. Almost all of these possible disadvantages accompanying the use of ALA can be ascribed to the physical-chemical properties of the molecule itself. Applied under physiological conditions, ALA is a zwitterion (Novo et al, 1996). Because the lipid bilayer of biological membranes is relatively impermeable to charged molecules, the cellular uptake of ALA is shallow. Consequently, in order to increase the transport across cellular membranes, fairly high drug doses and increased administration times have to be used. This deficiency results in a low penetration depth (Warloe et al, 1992;Loh et al, 1993;Peng et al, 1995) and an ALA-induced PpIX distribution, which is not optimized for the PDT of the deep layers of nodular lesions in the urothelium (Iinuma et al, 1995;Chang et al, 1996) after topical A...

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In a model of nude mice bearing a human colon carcinoma xenograft, the biodistribution and tumor localization of meta‐tetrahydroxyphenylchlorin (m‐THPC) coupled to polyethylene glycol (PEG) were compared with those of the free form of this photosensitizer used in photodynamic therapy (PDT). At different times after i.v. injection of both forms of 125I‐labeled photosensitizer, m‐THPC‐PEG gave on average a 2‐fold higher tumor uptake than free m‐THPC. In addition, at early times after injection, m‐THPC‐PEG showed a 2‐fold longer blood circulating half‐life and a 4‐fold lower liver uptake than free m‐THPC. The tumor to normal tissue ratios of radioactivity concentrations were always higher for m‐THPC‐PEG than for free m‐THPC at any time point studied from 2 to 96 hr post‐injection. Significant coefficients of correlation between direct fluorescence measurements and radioactivity counting were obtained within each organ tested. Fluorescence microscopy studies showed that m‐THPC‐PEG was preferentially localized near the tumor vessels, whereas m‐THPC was more diffusely distributed inside the tumor tissue. To verify whether m‐THPC‐PEG conjugate remained phototoxic in vivo, PDT experiments were performed 72 hr after injection and showed that m‐THPC‐PEG was as potent as free m‐THPC in the induction of tumor regression provided that the irradiation dose for m‐THPC‐PEG conjugate was adapted to a well‐tolerated 2‐fold higher level. The overall results demonstrate first the possibility of improving the in vivo tumor localization of a hydrophobic dye used for PDT by coupling it to PEG and second that a photosensitizer conjugated to a macromolecule can remain phototoxic in vivo. Int. J. Cancer 76:842–850, 1998.© 1998 Wiley‐Liss, Inc.

Autofluorescence is emerging as a useful tool for the detection of early cancers in the bronchi. It has already produced interesting results, which have been implemented in commercial imaging devices. Their design relies on the spectroscopy of the tissues of interest. However, a large majority of these autofluorescence spectroscopy studies have been presented in arbitrary units. This is a drawback for, in particular, the designing of imaging devices based on autofluorescence. Using correction factors and a spectral sensitivity correction curve, we determined the absolute spectral distribution of the tissue autofluorescence in vivo. These measurements were performed on healthy, metaplastic, and dysplastic bronchial tissues at several excitation wavelengths ranging from 350 to 495 nm. Moreover, we measured at a fixed distance between the tissue and the probe to avoid geometric distortions of the spectra that are due to the optical characteristics of tissue. We found that the order of magnitude of the autofluorescence brightness was stable as the excitation wavelengths varied (on the order of 5 pW/muW x nm at the maximum of the fluorescence emission spectra).