Huayun Shi*abc,
Muktesh Mohan
de,
Kanwarpal Singh
*def and
Peter J. Sadler
*a
aDepartment of Chemistry, University of Warwick, Coventry, CV4 7AL, UK. E-mail: Huayun.Shi@xmu.edu.cn; p.j.sadler@warwick.ac.uk
bState Key Laboratory of Vaccines for Infectious Diseases, Center for Molecular Imaging and Translational Medicine, Xiang An Biomedicine Laboratory, School of Public Health, Xiamen University, Xiamen, 361102, China
cState Key Laboratory of Molecular Vaccinology and Molecular Diagnostics, National Innovation Platform for Industry-Education Integration in Vaccine Research, Xiamen University, Xiamen, 361102, China
dMax-Planck-Institut für die Physik des Lichts, Staudtstraße 2, 91058 Erlangen, Germany. E-mail: kanwarpal.singh@mpl.mpg.de
eMax-Planck-Zentrum für Physik und Medizin, Kussmaulallee 2, 91054 Erlangen, Germany
fDepartment of Electrical and Computer Engineering, McMaster University, 1280 Main Street West, Hamilton, ON L8S 4K1, Canada
First published on 31st January 2025
Photoactive diazido Pt(IV) complexes display in vivo anticancer efficacy towards oesophageal tumours, a worldwide common cancer. Here we explore the use of optical coherence tomography (OCT) as a new method for detecting tissue penetration and damage produced by the photoactivatable anticancer complex trans,trans,trans-[Pt(pyridine)2(N3)2(OH)2] (FM190). Dehydration of the sample and a change in refractive index were observed for swine oesophageal tissue treated with FM190 and blue laser light (445 nm) using an OCT system. In contrast, tissues treated with FM190 or laser light alone showed no apparent damage.
Complexes in this class of Pt(IV) prodrugs are best activated by blue or green light which travels only ca. 1–3 mm into tissue.16 This makes them well suited for use in therapy of surface cancers such as bladder and oesophageal. Although red light with longer wavelength can penetrate more deeply (ca. 5 mm), this increases the risk of damage to deeper underlying normal tissue when treating surface cancers.17
We are therefore assessing methods, which can investigate the effects of these complexes on surface tissues both in the dark and in the light. The imaging technique of optical coherence tomography (OCT) uses short-coherence-length light and interferometry together with transverse scanning of the light beam to produce two- and three-dimensional images from light reflected from within biological tissues. Since its first use in 1991, it has become widely used for medical diagnosis, especially in ophthalmology for monitoring retinal, optic nerve and corneal diseases.18 It can rapidly achieve subsurface imaging at depths of 1–2 mm with simple sample preparation, and high-resolution subcellular micrometre resolution at low-cost.19–21
Lasers with high power output and easy connection to optical fibres and endoscopes can provide precise light delivery to tumours.17 The FM190 used in this work was synthesized and characterized as previously reported,13 and had a purity of >99%. The photoactivation of FM190 in aqueous solution with 445 nm laser light was very rapid due to the high intensity of light (250 mW cm−2), and was complete within 10 min (Fig. 1b).
The effect of FM190 on swine oesophageal tissue in the presence and absence of laser light exposure was determined using OCT. A phosphate-buffered saline (PBS) solution (200 μL) of FM190 with different concentrations (0, 100, 500 and 1000 μM) was dropped onto the mucosa of a piece of swine oesophageal tissue (ca. 1 × 1 cm2), which was then incubated at 310 K in the dark for 2 h. The tissue was scanned by the OCT system to obtain the morphology in the dark. After 10 min irradiation with blue laser light (445 nm), the same area of this tissue was scanned again to determine the morphology after light exposure.
The attenuation coefficient is a crucial parameter in OCT signal analysis. It is a measure of the decay of light intensity within the sample due to absorption and scattering, and can be calculated with the aid of the Beer–Lambert law, which can be expressed as eqn (1).22,23
I = I0![]() | (1) |
μA = μs + μa | (2) |
To evaluate the attenuation coefficient, we extracted the optical characteristics of the incident light beam at any spot over the tissue surface, which involved extracting the optical characteristics of the incident light beam.
During OCT data acquisition, a coherence beam of light is scanned over the sample surface to extract the depth information. Backscattered light preserves the tissue characteristics within it. OCT volumetry data are a collection of A-scans, also known as depth-resolved interferometry signals arranged over the scan surface (Fig. 2). A schematic diagram of the OCT system used in shown in Fig. S1 (ESI†). To evaluate the attenuation coefficient, we extracted an average of 10 A-scans from the B-scan (cross-sectional OCT image) to reduce noise. Part of the A-scan signal consists of tissue characteristic information, which was then exponentially fitted. The coefficient values are equated to the corresponding depth information (see eqn (1)). The attenuation coefficient value was calculated over the whole scanning length of the tissue, and statistical analysis was performed for every sample.
![]() | ||
Fig. 2 Steps involved in attenuation coefficient calculation. Coefficients for curve-fitted values were divided by the round-trip distance covered by imaging light. Scale bars in B-scan: 500 μm. |
After 2 h incubation of swine oesophageal tissue with FM190 in the dark at 310 K, all tissues remained intact and smooth. FM190 acts as a high scattering media for imaging beams of light and thus enhances the contrast of the internal structure (Fig. 3). The enhanced contrast shows that it was absorbed very well deeply into the tissue. When FM190 was activated with a pump laser and interacts with the tissue, this resulted in dehydration of the sample and a change in refractive index. The combined effect changes the morphological structure, as can be observed from comparative images. From the internal microstructures, the field of view becomes restricted due to an increased refractive index, which results in higher attenuation coefficient values. In contrast, the negative control treated with light alone exhibits no apparent changes in morphology and a similar attenuation coefficient compared with the dark control. These results confirm the low dark cytotoxicity of FM190 and damage to the mucosa of swine oesophagus induced by the combination of FM190 and blue laser light. The rapid observation of damage is consistent with the release and formation of reactive azidyl radicals, oxygen species (ROS), as well as photosubtituted Pt(IV) and reduced Pt(III) and Pt(II) species.13,14 These findings confirm the potential application of FM190 in the treatment of oesophageal cancers as a photoactive prodrug with a new mechanism of action and low side effects.
This is the first exploration of the effect of the photoactivatable Pt(IV) prodrug FM190 on oesophageal tissue in the absence and presence of light using an OCT system. The significant changes in the mucosa of swine oesophagus before and after irradiation suggest the low dark cytotoxicity and promising photocytotoxicity of FM190, which is a promising property of this candidate photoactive anticancer prodrug. The application of OCT technology in the visualisation of the internal structure of biological tissues allows the exploration of drug and light penetration in phototherapy, which can guide the design of new photoactive prodrugs.
Footnote |
† Electronic supplementary information (ESI) available. See DOI: https://doi.org/10.1039/d4ra08693g |
This journal is © The Royal Society of Chemistry 2025 |