Advances in Purpurin 18 Research: On Cancer Therapy

: How to make cancer treatment more efﬁcient and enhance the patient’s outcome? By multimodal therapy, theranostics, or personalized medicine? These are questions asked by scientists and doctors worldwide. However, ﬁnding new unique approaches and options for cancer treatment as well as new selective therapeutics is very challenging. More frequently, researchers “go back in time” and use already known and well-described compounds/drugs, the structure of which further derivatize to “improve” their properties, extend the use of existing drugs to new indications, or even to obtain a completely novel drug. Natural substances, especially marine products, are a great inspiration in the discovery and development of novel anticancer drugs. These can be used in many modern approaches, either as photo- and sonosensitizers in photodynamic and sonodynamic cancer therapy, respectively, or in tumor imaging and diagnosis. This review is focused on a very potent natural product, the chlorophyll metabolite purpurin 18, and its derivatives, which is well suitable for all the mentioned applications. Purpurin 18 can be easily isolated from green plants of all kinds ranging from seaweed to spinach leaves and, thus, it presents an economically feasible source for a very promising anticancer drug. mainly PDT and PTT. Pu18, as well as other PSs, is also able to absorb energy delivered into tumors by ultrasound, which is used in SDT. Both PDT and SDT might be also combined with cancer diagnostics and, thus, pu18 can act as a theranostic agent. In the following chapters, we discuss the basics of all these approaches as well as the potential therapeutic and diagnostic roles of pu18 and its derivatives in cancer. mice with Luc-HepG2 tumors showed preferential accumulation of NGR ® DDP in tumor tissue as well as significant reduction or complete disappearance of the tumor after administration of NGR ® DDP in combination with an ultrasound. Besides, histological analysis showed extensive tumor tissue damage with minimal damage of normal/healthy tissues, thus suggesting high drug selectivity with the generation of minimal side effects. cytotoxic peptide Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys (KLAK-LAK), the ST pu18, and PEG, which is attached by a thiol bond. After PTPK treatment with ultrasound, pu18 is activated to form singlet oxygen, which leads to cleavage of the thiol bond and cleavage of the PEG spacer. The rest of the SH-(pu18) KLAK molecule then forms self-assembled nanoparticles due to increased hydrophobicity. The nanoparticles are then transported into cells by endocytosis (Figure 7). Cytotoxicity assays on the Panc-1 cell line show that PTPK exhibits higher cytotoxicity and higher mitochondrial damage to treated cells after ultrasound treatment compared to non-cleavable PEG (pu18) KLAK and pre-prepared (pu18)-KLAK nanoparticles (without PEG). Using a multicellular tumor spheroid of Panc-1 cancer cells, the ability of single-stranded PTPKs to penetrate deeper into tissues was observed than with pre-packaged (pu18)-KLAK nanoparticles. In situ packaging of nanoparticles is also likely to lead to improved cell transport through endocytosis. Tests on nude mice implanted with Panc-1 cells have shown that PTPK in combination with ultrasound inhibits the growth of subcutaneous and orthotopic tumors. of purpurin 18 (pu18) and NH 4 HCO 3 (in the hydrophilic core of the particle) are incorporated. Under the action of laser irradiation, the pu18 aggregates are activated to produce heat and a photoacoustic (PA) signal. The generated heat activates the slow decomposition of NH 4 HCO 3 , with the formation of CO 2 bubbles. This ensures a long-term increase in the PA signal, which can be easily detected for several hours [78]. observed for the next 24 h. Observed PA signal after application of pu18-PLGVRGRGD, range of double values compared to pu18-PLGVRGRDG (no target sequence), indicating increased accumulation of pu18-PLGVRGRGD in the tumor. The formation of nanoﬁbers directly at the tumor site can also lead to a prolongation of the retention time of the probe in the tumor tissue (so-called assembly/aggregation-induced retention). The half-life of pu18-PLGVRGRGD is almost 24 h, which is six times more than in the case of the control probe pu18-PMGMRGRGD with a change in the peptide sequence that is not recognized by gelatinase (does not form nanoﬁbers). In a long-term experiment with U87-xenografted mouse cells, complete tumor disappearance occurred after 23 days of treatment with the pu18-PLGVRGRGD probe in combination with laser treatment. The histopathological analysis did not prove damage to other organs (the heart, liver, kidneys, lungs), while the tumor tissue showed signs of necrosis. up to four times 10). Cytotoxicity assays on the HeLa, MCF-7, and L929 cell lines showed increased cytotoxicity and higher number of apoptotic cells treated with PKK-S-PEG in combination with laser illumination than in non-illuminated cells. Due to the assay on BALB/c mice transplanted with Hela cells, increased accumulation and retention time of the drug in the tumor tissue was observed. Due to the formation of photoacoustic waves, it was possible to monitor the formation of nanoﬁbers and the movement of the drug in real-time. shows the chemical structure of the polymer-peptide conjugate PKK-S-PEG. It is composed of the cytotoxic peptide Lys-Leu-Ala-Lys-Lu-Ala-Lys (KLAKLAK), which binds to the mitochondrial membrane, a hydrogen-bonding peptide motif Lys-Leu-Val-Phe-Phe (KLVFF, originated from the A β protein), the hydrophobic unit of poly(ethylene glycol) = PEG, which is attached via a disulﬁde bridge, and the photoacoustic/photothermal molecule pu18. Drug monomers are spontaneously packaged into nanoparticles, which are transported into cells by endocytosis. Upon entering the cells, the PEG chain is cleaved leading to the spontaneous transformation of nanoparticles (NPs) into mitochondrially targeted nanoﬁbers (NFs). The conversion in NFs can be accelerated photothermally [83]. be cleaved to form highly organized nanoﬁbers (NFs) upon transition to the acidic environment of tumor cells. The conversion of NPs to NFs can be monitored in real-time using photoacoustic imaging [84].


Introduction
Cancer and the lack of an effective treatment have been global problems for many years. Current treatment approaches are based on decades-old methods such as tumor resection, radiotherapy, and classic chemotherapy, which are not always effective and, thus, cancer remains to be the leading cause of death worldwide [1]. Significant problems of current anticancer therapy are especially the low selectivity of anticancer drugs and their high systemic toxicity, which leads to damage of healthy cells. A severe obstacle in cancer treatment is also the frequent emergence of resistance to individual chemotherapeutics, whether it is a natural resistance or acquired, for example, due to insufficient drug concentration at the tumor site. Modern strategies for cancer treatment include early diagnosis of the disease as well as effective targeted treatment with minimal side effects. To the long-known methods with such benefits belongs photodynamic therapy (PDT), which is based on the application of a photosensitive substance (PS), which after excitation by light and reaction with cellular oxygen generates cytotoxic reactive oxygen species (ROS) [2]. Very similar methods closely related to PDT are photothermal therapy (PTT) and sonodynamic therapy (SDT). In PTT, the light energy absorbed by a PS is converted into thermal energy. The generated heat then warms the target tumor cells, which leads to their damage and death. In the case of SDT, instead of light, ultrasound waves are applied to activate the drug used, a so-called sonosensitizer (ST). Then, the activated ST eliminates the target cells by a similar mechanism to that of a PS. In addition to SDT, another method utilizes acoustic ultrasonic waves-photoacoustic imaging (PAI). However, as for PAI, the ultrasound As the structural formulas are shown in Figure 1, it is apparent that Chl is a porphyrin with a cyclic tetrapyrrole nucleus. Its metabolites are characterized by 18π electrons in the aromatic ring with a conjugated double bond system. This structural arrangement predetermines Chl metabolites to be PSs with the possibility of use for example in cancer therapy. Chla itself is characterized by a high extinction coefficient at 661 nm [16] and good singlet oxygen production. However, what limits its further use is its low thermal stability, proneness to degradation due to light irradiation, and also low stability at acidic pH. At the same time, it was found that Chla exhibits lower thermal and pH stability than Chlb [17]. Therefore, from the point of view of a PS, its natural degradation products and their semi-synthetic derivatives are more interesting for potential medicinal application.

Purpurin 18 and Cancer Treatment
One of such degradation products of Chl is the already aforementioned pu18, a photosensitive chlorin substance naturally occurring in, for example, spinach leaves [18], cyanobacterium Spirulina maxima [19], Japanese carpet shells Ruditapes phlippinarum [20], brown mussel Perna perna [21], or in a whole series of edible seaweed [22]. It has been confirmed that pu18 can be even observed from geological samples of sediments [23]. Considering mainly its photochemical properties, pu18 represents a potentially useful substance for cancer phototherapy. What is mainly advantageous is its maximum absorption at 700 nm, as the light of such wavelength penetrates deep into the tumor tissue [24]. Unfortunately, even despite this benefit, pu18 has not been applied in clinical practice, yet, since it exhibits high hydrophobicity. Therefore, tremendous effort has been made to

Purpurin 18 and Cancer Treatment
One of such degradation products of Chl is the already aforementioned pu18, a photosensitive chlorin substance naturally occurring in, for example, spinach leaves [18], cyanobacterium Spirulina maxima [19], Japanese carpet shells Ruditapes phlippinarum [20], brown mussel Perna perna [21], or in a whole series of edible seaweed [22]. It has been confirmed that pu18 can be even observed from geological samples of sediments [23]. Considering mainly its photochemical properties, pu18 represents a potentially useful substance for cancer phototherapy. What is mainly advantageous is its maximum absorption at 700 nm, as the light of such wavelength penetrates deep into the tumor tissue [24]. Unfortunately, even despite this benefit, pu18 has not been applied in clinical practice, yet, since it exhibits high hydrophobicity. Therefore, tremendous effort has been made to derivatize pu18 structure to overcome this solubility limitation. The chemical structure of pu18 offers great options for structural modifications (Figure 2). One example among many is linking pu18 with a peptide by a reaction of the carboxyl group of propionic acid of pu18 and amidogen radical of the peptide. For example, by linking pu18 with arginine-rich peptides, conjugates with higher hydrophilicity can be prepared, which, besides, exert modified aggregation properties (increased with a higher number of arginine units) and well-ordered assembly [25]. That is, indeed, another advantage of pu18. Its macrocyclic nature makes it an ideal structural unit for creating larger entities by the supramolecular assembly. This property could be used in cancer treatment and imaging (see Chapter 9), as certain peptide-conjugated pu18 derivatives can create in situ nanofibers and, thus, prolong retention time in tumors and, thus, enable improved imaging opportunities and more effective therapeutical outcome [26]. Therapy with pu18 is, as aforementioned, based mainly on its photosensitivity. This phenomenon is utilized in diverse therapeutical approaches, mainly PDT and PTT. Pu18, as well as other PSs, is also able to absorb energy delivered into tumors by ultrasound, which is used in SDT. Both PDT and SDT might be also combined with cancer diagnostics and, thus, pu18 can act as a theranostic agent. In the following chapters, we discuss the basics of all these approaches as well as the potential therapeutic and diagnostic roles of pu18 and its derivatives in cancer.
prolong retention time in tumors and, thus, enable improved imaging opportunities and more effective therapeutical outcome [26]. Therapy with pu18 is, as aforementioned, based mainly on its photosensitivity. This phenomenon is utilized in diverse therapeutical approaches, mainly PDT and PTT. Pu18, as well as other PSs, is also able to absorb energy delivered into tumors by ultrasound, which is used in SDT. Both PDT and SDT might be also combined with cancer diagnostics and, thus, pu18 can act as a theranostic agent. In the following chapters, we discuss the basics of all these approaches as well as the potential therapeutic and diagnostic roles of pu18 and its derivatives in cancer.

Figure 2.
Numbered molecular structure of purpurin 18 (pu18) and positions of frequent modifications. The pu18 molecule is usually modified to improve its photochemical properties, for example, by halogenation (violet dots) or nitration (orange dots), or derivatized by conjugation reactions with peptides or other tumor cell-targeting molecules. The most common approaches are the use of a free carboxyl group (C-173) to form esters or amides (an orange dot) or by the derivatization of a cyclic anhydride to form imides (a blue dot).

Photodynamic Therapy
PDT is an attractive approach to the treatment of many types of cancer and non-cancerous diseases. This approach is based on the administration of photoactive substances, so-called PSs, which themselves (without any stimulation) do not exhibit any biological activity. They are activated by illumination with light of appropriate wavelength upon which a PS transits into an excited state. Then, the excited PS can react with molecular oxygen to form ROS and singlet oxygen. The presence of these particles in a cell leads to strong oxidative stress resulting in cell damage and cell death ( Figure 3). However, ROS play a dual role in cancer treatment, since they can trigger multiple cellular cascades leading also to pro-tumorigenesis [27]. The ideal PS should meet several criteria, such as high quantum yield of singlet oxygen and absorption in the dark red or near-infrared region of the electromagnetic spectrum (650-800 nm), which ensures deeper penetration of the light into a treated tissue. On the contrary, negligible absorption of the PS in the visible part electromagnetic spectrum (400-600 nm) is desirable due to possible photosensitization of the skin [28]. Excitation and emission spectra are very important properties of PSs because human tissue contains many endogenous chromophores that also absorb light. For example, hemoglobin, myoglobin, melanin, and water absorb light in the 600-1000 nm region, which limits the biological window in this range of wavelengths [29]. Therefore, current trend is to develop novel PSs absorbing in the range of the second and third near-infrared (NIR) region of the electromagnetic spectrum (NIR-II: 1000-1350 nm, NIR-III: 1550-1870 nm), which provides the benefit of deeper tissue penetration, enhanced image contrast Figure 2. Numbered molecular structure of purpurin 18 (pu18) and positions of frequent modifications. The pu18 molecule is usually modified to improve its photochemical properties, for example, by halogenation (violet dots) or nitration (orange dots), or derivatized by conjugation reactions with peptides or other tumor cell-targeting molecules. The most common approaches are the use of a free carboxyl group (C-173) to form esters or amides (an orange dot) or by the derivatization of a cyclic anhydride to form imides (a blue dot).

Photodynamic Therapy
PDT is an attractive approach to the treatment of many types of cancer and noncancerous diseases. This approach is based on the administration of photoactive substances, so-called PSs, which themselves (without any stimulation) do not exhibit any biological activity. They are activated by illumination with light of appropriate wavelength upon which a PS transits into an excited state. Then, the excited PS can react with molecular oxygen to form ROS and singlet oxygen. The presence of these particles in a cell leads to strong oxidative stress resulting in cell damage and cell death ( Figure 3). However, ROS play a dual role in cancer treatment, since they can trigger multiple cellular cascades leading also to pro-tumorigenesis [27]. The ideal PS should meet several criteria, such as high quantum yield of singlet oxygen and absorption in the dark red or near-infrared region of the electromagnetic spectrum (650-800 nm), which ensures deeper penetration of the light into a treated tissue. On the contrary, negligible absorption of the PS in the visible part electromagnetic spectrum (400-600 nm) is desirable due to possible photosensitization of the skin [28]. Excitation and emission spectra are very important properties of PSs because human tissue contains many endogenous chromophores that also absorb light. For example, hemoglobin, myoglobin, melanin, and water absorb light in the 600-1000 nm region, which limits the biological window in this range of wavelengths [29]. Therefore, current trend is to develop novel PSs absorbing in the range of the second and third nearinfrared (NIR) region of the electromagnetic spectrum (NIR-II: 1000-1350 nm, NIR-III: 1550-1870 nm), which provides the benefit of deeper tissue penetration, enhanced image contrast due to reduced optical scattering, and lower phototoxicity [30]. Related to this, it is another important property of a PS-preferred and ideally selective accumulation of the PS in the target, usually tumor, tissue. Equally important in PDT is none or marginal dark toxicity (without photoactivation) of the PS and its potential metabolites. What makes the use of PDT for cancer treatment more advantageous over conventional surgical methods are its low invasiveness and minimal side effects, which are frequently encountered in chemotherapy and radiotherapy. For this reason, PDT has been a very attractive method in cancer treatment.

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low invasiveness and minimal side effects, which are frequently encountered in chemotherapy and radiotherapy. For this reason, PDT has been a very attractive method in cancer treatment. Figure 3. A general principle of photodynamic therapy (PDT). PDT is based on the action of light radiation on a photosensitive drug (PS). After receiving energy, it passes into a higher energy state. Then, it transfers the received energy to surrounding molecules and turns back to its ground state. In the energy transfer mechanism Type I, the energy is transferred to a biomolecule which reacts with 3 O2 to form reactive oxygen species (ROS). During the Type II transfer, there is a direct reaction of the PS with the 3 O2 molecule, with the formation of singlet oxygen 1 O2, which also belongs to the ROS.
In PDT, substances originating in natural products are often used as PSs, including the already mentioned pu18. Pu18 in connection to photoactivation has attracted scientific interest already more than thirty years ago when Hoober et al. [18] discovered that photoactivated pu18 inhibits the growth of primary human fibroblasts. Thirteen years later, after the reports that photoactivated pu18 induces apoptosis and necrosis also in human cancer cells, namely HL-60 (cells from leukemia) [31,32], the real boom in pu18 research related to cancer treatment has started.
More recently, pu18 has been tested as an effective PS for PDT treatment of commonly incurable triple-negative breast cancer [33]. The phototoxicity of pu18 was determined using a mouse mammary tumor cell line (4T1), which is used as a model of stage IV human breast cancer. 4T1 cells were used in the form of two-dimensional (2D) culture, three-dimensional (3D) spheroids, and, also, in vivo in Balb/c mice with subcutaneously implanted 4T1 cells. In the case of 4T1 2D cell cultures, significant phototoxicity of pu18 (0.5 μM) was observed after light illumination at 630 nm (35 s, 3.71 J·cm −2 ). Without photoactivation, pu18 did not exhibit any signs of toxicity up to 4 μM concentration. During the microscopic analysis of PDT-treated cells, a change in the cell shape (size reduction, rounding, vacuolation) and their separation from the surface of the culture dish was de- PDT is based on the action of light radiation on a photosensitive drug (PS). After receiving energy, it passes into a higher energy state. Then, it transfers the received energy to surrounding molecules and turns back to its ground state. In the energy transfer mechanism Type I, the energy is transferred to a biomolecule which reacts with 3 O 2 to form reactive oxygen species (ROS). During the Type II transfer, there is a direct reaction of the PS with the 3 O 2 molecule, with the formation of singlet oxygen 1 O 2 , which also belongs to the ROS.
In PDT, substances originating in natural products are often used as PSs, including the already mentioned pu18. Pu18 in connection to photoactivation has attracted scientific interest already more than thirty years ago when Hoober et al. [18] discovered that photoactivated pu18 inhibits the growth of primary human fibroblasts. Thirteen years later, after the reports that photoactivated pu18 induces apoptosis and necrosis also in human cancer cells, namely HL-60 (cells from leukemia) [31,32], the real boom in pu18 research related to cancer treatment has started.
More recently, pu18 has been tested as an effective PS for PDT treatment of commonly incurable triple-negative breast cancer [33]. The phototoxicity of pu18 was determined using a mouse mammary tumor cell line (4T1), which is used as a model of stage IV human breast cancer. 4T1 cells were used in the form of two-dimensional (2D) culture, three-dimensional (3D) spheroids, and, also, in vivo in Balb/c mice with subcutaneously implanted 4T1 cells. In the case of 4T1 2D cell cultures, significant phototoxicity of pu18 (0.5 µM) was observed after light illumination at 630 nm (35 s, 3.71 J·cm −2 ). Without photoactivation, pu18 did not exhibit any signs of toxicity up to 4 µM concentration. During the microscopic analysis of PDT-treated cells, a change in the cell shape (size reduction, rounding, vacuolation) and their separation from the surface of the culture dish was detected. Flow cytometry analysis showed that PDT treatment of 4T1 cells using 0.5 µM pu18 (0.724 J·cm −2 ) successfully induced apoptosis in 50 % of the cells. For 4T1 cells cultured as 3D spheroids, the cells were exposed to 4 µM pu18 for 24 h and were photoactivated at 630 nm (4 min, 25.2 J·cm −2 ), and further cultured for 6 days. On the second day after PDT, a decrease in the mean of 4T1 spheroids was observed compared to the control group. However, further cultivation showed that in the PDT-treated group, cell growth was not completely inhibited, since the 4T1 spheroids were further increasing their volume. However, it was slower than in the case of PDT-untreated 4T1 spheroids. The PDT effect of pu18 administered intratumorally was verified using experimental Balb/c mice with subcutaneously implanted 4T1 cells. After PDT treatment (pu18, 0.625 mg·kg −1 , 600 J·cm −2 ), the tumor size was monitored every second day for two weeks. Six days after PDT, a significant decrease in the tumor volume (60%) was observed in the PDT-treated group compared to control groups, in which a constant growth of the tumors was observed. Although PDT significantly suppressed the size of the tumor, its overall disappearance did not occur here either. However, the survival time of PDT-treated mice was longer compared to the control group. The obtained results indicate a high efficacy of pu18 as a potent PS for the use in PDT. Nevertheless, there are still big weaknesses of high pu18 hydrophobicity (leading to the formation of pu18 aggregates), low bioavailability (difficult delivery of pu18 to a tumor tissue), and rapid removal from the tumor tissue [33]. Researchers have tried to solve these shortcomings by derivatization of the pu18 structure, such as creating imides, or anhydrides [34][35][36][37], conjugating it to a molecule of a carrier or creating various types of pu18-containing nanoparticles.
A solution to reduce pu18 hydrophobicity and improve its bioavailability is, for example, conjugation of pu18 with a polyethylene glycol (PEG) spacer, as described in our previous article [38]. It was observed that the newly prepared PEGylated pu18 conjugates efficiently accumulated in human cancer cells of various origins (breast-MCF-7, prostate-PC-3 and LNCaP, cervix-HeLa, and pancreas-MiaPaCa-2) in vitro with preferential localization in PDT of important organelles such as mitochondria and endoplasmic reticulum (ER). Attachment of the PEG 3 arm also led to an increase in phototoxicity after light illumination (4 J·cm −2 , 13 min) compared to the parental compound. The increase in phototoxicity was probably due to the increase in the conjugate hydrophilicity and, thus, improved solubility of the compound in aqueous media. This further led to a reduction in the formation of pu18 aggregates and better drug bioavailability. To increase the PEGylated conjugate modality, it was further modified with a zinc ion which was incorporated into the pu18 structure. The presence of a zinc ion led to an increase in the absorption in the red region of the visible spectrum, which could enable also imaging of this compound.
Besides PEGylation, conjugating of pu18 to biocompatible graphene oxide (GO), has been described. Thanks to its unique surface properties (carboxyl, hydroxyl, and epoxy groups, free π electron, pH-dependent negative surface charge), GO can bind drug molecules and, thus, contribute to their efficient transport into tumor cells. The properties of GO as a PS carrier were used in the work of Zhang et al. [39], who prepared GO-Pu18 conjugates composed of GO with non-covalently bound (π-π stacking, hydrophobic interactions) pu18 methyl ester, with the aim to increase water solubility, improve bioavailability, control pH-release of pu18 and possibly use in theranostics (see Chapter 9). A similar approach was used by Kang et al. [40], who prepared two types of nanoparticles GO-PS2 and GO-PS3, composed of GO as a carrier and pu18-N-ethylamine as a PS. These nanoparticles differed from each other in the type of bonds in the molecule, GO-PS2 contained covalently bound PS, which led to the high stability of the particles under different conditions. In contrast, GO-PS3 contained, like the aforementioned GO-pu18, non-covalently bound PS, which was released at a slightly acidic pH ( Figure 4A). Based on the microscopic examination, it was found that all prepared conjugates (GO-Pu18, GO-PS2, GO-PS3) are transported into human tumor cells (HepG2, A549) to a greater extent than the unconjugated pu18. Increased phototoxicity of conjugates GO-Pu18 (HepG2 cell line, xenon lamp, 700 nm, 5 mW·cm −2 , 10 min) and GO-PS2, GO-PS3 (A549 cell line, laser, 610-710 nm, 2 J·cm −2 , 15 min) vs. free pu18 after photoactivation was detected. Dark toxicity (without photoactivation) corresponded to a free PS for GO-pu18 and GO-PS2 conjugates. No toxicity was observed for GO-PS3 in the specified concentration range. Although GO-PS3 showed a lower rate of 1 O 2 generation compared to free pu18 (in vitro), higher PDT activity was determined for GO-PS3. This was probably due to the more efficient delivery of GO-PS3 to the cells and the release of non-covalently bound pu18-N-ethylamine in the acidic environment of the tumor cells. Both research groups have shown that GO can be a suitable carrier for the efficient delivery of a PS to cancer cells. From the point of view of the targeted release of a PS in tumor tissue, it is advantageous to use noncovalent binding for linking the carrier to the PS molecule.
Currently, great potential in the development of PSs for PDT have nanoparticles. These can be used, for example, for reducing the PS hydrophobicity and to improve its bioavailability. This approach was chosen by Liu et al. [41], who prepared three types of water-soluble organic nanoparticles (WSONs) containing chlorine derivatives such as PS: methyl pyropheophorbide a (MPPa), zinc metal-introduced MPPa (ZnMPPa), and pu18 methyl ester (pu18ME). All prepared WSONs reached a size of 87-112 nm and showed good solubility and stability in water. Fluorescence microscopy analysis showed the entry of all WSONs into human HeLa tumor cells and their localization in mitochondria. High phototoxicity of WSONs after light-emitting diode (LED) illumination was also recorded (640-710 nm, 2 J·cm −2 , 15 min) which corresponded to the parental PS. The newly prepared WSONs thus preserve or even improve the properties of the original PS, such as absorption in the red region of the visible spectrum, high phototoxicity, and reduced dark toxicity. Besides, the high solubility of WSONs ensures good bioavailability compared to free PS.
Additionally, other research groups have been involved in increasing PS bioavailability. Since gold nanoparticles (GNPs) represent a promising system for pu18 delivery and ensure better entry into tumor cells, recently the group of Lie et al. [42] utilized this tool. They synthesized ionic liquid (IL)-dependent GNPs with pu18 ( Figure 4B). This system is based on the properties of water-soluble ILs that can promote increased solubility of conjugated PSs [42]. It has also been reported that ILs can increase drug stability, promote drug delivery, and controlled release [43]. The prepared drugs consisted of IL-type PSs (PS1 = pu18 + morpholinium, PS2 = pu18 + imidazolium), which were incorporated into GNPs (GNP1 contains 492 nmol·mg −1 PS1 and GNP2 contains 573 nmol·mg −1 PS2) to give 20-60 nm large spherical particles. The phototoxicity of the newly prepared GNP1 and GNP2 was verified using the A549 cell line and illumination with a light-emitting diode (735-785 nm, 2 J·cm −2 , 15 min). In the case of GNP1, a 34-and 37-fold increase in phototoxicity was observed compared to free PS1 (12 and 24 h after photoactivation, constant IC 50 = 0.38 g·mL −1 ) and no observable dark toxicity. Besides, microscopic analysis of GNP1-treated cells in combination with light showed the presence of apoptotic bodies. In contrast, GNP2 showed low phototoxicity at 12 h after illumination (IC 50 > 20 µg·mL −1 ) and after 24 h, only 3.6-fold higher phototoxicity (IC 50 = 4.34 µg·mL −1 ) compared to free PS2. Besides, moderate dark toxicity was determined for both GNP2 and PS2. Thus, it is clear that in the formation of nanoparticles, the type of IL used, and its properties were of great importance.
11, x FOR PEER REVIEW 8 of Figure 4. Various types of modifications of purpurin 18 (pu18) may lead to an improvement in it properties as a photosensitizer for use in photodynamic therapy. (A) The first approach is to use suitable carrier such as graphene oxide (GO) to increase the bioavailability of pu18. In this case, two types of GO nanoparticles were prepared with pu18-N-ethylamine (pu18NEA) and a photosensitizer (PS), via covalent (GO-PS2) and non-covalent bonds (GO-PS3). (B) Another type of na noparticles is based on the properties of ionic liquids (IL), which together with pu18 were incorp rated into gold nanoparticles (GNP1 and GNP2) and the structure of pu18-methyl ester (pu18Me (C) Improved PS retention in tumor cells was observed in the case of conjugated drug pu18 with the amine spermine. In the case of the attachment of a poly(ethylene) glycol (PEG) spacer, an increase in hydrophobicity and an improvement in the bioavailability of PS were observed [44].
Nanoparticles can also play an important role in targeted drug delivery to minimi The first approach is to use a suitable carrier such as graphene oxide (GO) to increase the bioavailability of pu18. In this case, two types of GO nanoparticles were prepared with pu18-Nethylamine (pu18NEA) and a photosensitizer (PS), via covalent (GO-PS2) and non-covalent bonds (GO-PS3). (B) Another type of nanoparticles is based on the properties of ionic liquids (IL), which together with pu18 were incorporated into gold nanoparticles (GNP1 and GNP2) and the structure of pu18-methyl ester (pu18Me). (C) Improved PS retention in tumor cells was observed in the case of conjugated drug pu18 with the amine spermine. In the case of the attachment of a poly(ethylene) glycol (PEG) spacer, an increase in hydrophobicity and an improvement in the bioavailability of PS were observed [44].
Nanoparticles can also play an important role in targeted drug delivery to minimize treatment side effects. As an example, SiO 2 nanoparticles (SiO 2 NPs) [45] have several advantages, in particular, nontoxicity and high stability as well as compatibility with various PSs including pu18, chlorine [46], methylene blue [47], and hematoporphyrin [48,49]. The group of Cao et al. used mesenchymal stem cells (MSCs) as pu18 transporters in the form of PS-SiO 2 NPs nanoparticles for targeting breast cancer tumor cells [45]. It is known that MSCs naturally show a high affinity for tumor cells [50,51]. The generated PS-SiO 2 NPs-MSCs particles migrated to human breast cancer cells (MCF-7), which means that the content of PS-SiO 2 NPs does not negatively affect the targeting of MSCs and pu18 can thus be accumulated in targeted cells. At the same time, it was found that PS-SiO 2 NPs-MSCs inhibited the growth of MCF-7 cells after PDT treatment, both in the form of 2D culture in vitro and in vivo in nude mice with subcutaneously transplanted MCF-7 cells, in which there was a reduction in tumor size and weight. When PS-SiO 2 NPs were introduced into human embryonic kidney cells (HEK-293) instead of MSCs, no significant PDT effect on cell viability was detected since there was no targeted localization of the drug into the tumor cells [38]. The use of MSCs seems a promising strategy for targeted drug delivery to tumor cells.
A long-term approach in the treatment of cancer is a so-called multimodal therapy which may lead mainly to a reduction in the resistance of tumor cells to anticancer chemotherapeutics. This may be, for example, a combination of tumor resection with chemotherapy, a combination of chemotherapy with PDT, or administration of a multimodal drug. Recently, researchers at Southwest University have developed photo-/chemotherapeutics containing pu18 as a PS [52,53]. The first is a nanogel-based drug (DHP NGs~67 nm) composed of pu18, the chemotherapeutic 10-hydroxycamptothecin (HCPT), a redox responsive cross-linking agent, glutathione responsive spacer, and a PEG spacer to increase particle stability. The second multimodal drug contains doxorubicin (DOX) and pu18 encapsulated in PDP micelles (~148 nm) composed of mono (6-amino-6-deoxy)-β-cyclodextrin with a ROS-sensitive polymer containing borate bonds. Both types of drugs have been designed to preferentially accumulate in a tumor tissue based on enhanced permeation and retention effects, for tumor tissue imaging as well as selective drug release due to increased GSH/ROS production by tumor cells. In mouse tumor cell line 4T1, the ability to enter cells, localize in lysosomes and mitochondria, reduce membrane potential of mitochondria and cause cell death has been confirmed [53]. In assays in Balb/c mice implanted with 4T1 cells, longer retention time, and better distribution of DHP NGs in tumor tissue compared to free pu18 were detected, as well as a significant reduction of tumor volume after laser exposure (660 nm, 0.5 W·cm −2 , 5 min). Immunohistochemical analysis of tumor cells subsequently revealed a large number of necrotic and apoptotic cells due to combined photo-/chemotherapy, the treatment did not cause any obvious damage to other organs (the liver, kidneys, heart, and lungs). Very similar results were obtained for the second drug PDP in combination with the same laser treatment. Upon this treatment, only 17.17% of 4T1 cells survived compared to 40.89 % for pure DOX and 61.28% for pure pu18 in combination with irradiation. Very similar results, as for the first drug, were shown also in experiments on Balb/c mice implanted with 4T1. Both drugs thus represent a significant step in the combined therapy of tumors. A summary of the aforementioned studies on pu18 and its derivatives in PDT is covered in Table 1. Table 1. Summary of purpurin 18 (pu18) applications and its derivatives aimed for photodynamic therapy (PDT) using human (HL-60, LNCaP, PC-3, MiaPaCa-2, HeLa, MCF-7, HepG2, A549) and mouse (4T1) cell line models. IC 50 -half-maximal inhibitory concentration after 24 h treatment with pu18, Light-after pu18 photoactivation, dark-without photoactivation, growth inhibition-in studies, where no IC 50 was calculated, the compound potency was expressed by percentage of growth inhibition at a certain concentration.

Drug
Cell Line Light Dose IC 50 Light IC 50 Dark Growth Inhibition Light Ref.

Sonodynamic Therapy and Sonophotodynamic Therapy
Another noninvasive approach of cancer treatment is sonodynamic therapy (SDT). It is a method discovered and derived based on PDT. In PS evaluation, it was found that, for example, porphyrin [54][55][56][57], pheophorbide [57,58], and/or pu18 derivatives [59] used in PDT show similar effects and cell damage after ultrasound application as detected after photoactivation. The main principle of SDT is identical to PDT. The SDT method is based on a combination of low-intensity ultrasound and a sonosensitive agent (ST), which is activated by ultrasound ( Figure 5). However, the mechanism of ST activation and ROS formation in SDT is not exactly known. The action of ultrasound generates heat in the target tissue and, also, acoustic cavities. These can occur in two states: stable cavities, which oscillate in an aqueous environment, leading to fluid flow, and inertial cavities, which are characterized by rapid enlargement and subsequent sharp collapse (implosion). During the collapse of these cavities, a large amount of heat (≥5000 K) and pressure (≥800 atm.) is released [60,61]. This can lead to a series of chemical reactions inside, on, or around the collapsing cavitation bubble, which is often referred to as a sonochemical reactor [62]. Typically, pyrolysis or thermal dissociation of water may occur here, which may lead to ST activation and, also, to ROS production.
11, x FOR PEER REVIEW 11 of 24 Figure 5. General principles of sonodynamic therapy. The action of ultrasound activates the sonosensitive agent and its transition to a higher energy state. When returning to the basic energy state, the energy generated is transformed in the form of heat, acoustic cavities, or light (sonoluminescence). As a result of these processes, reactive oxygen species (ROS) are formed, which leads to damage of the mitochondrial membrane, the release of cytochrome c (cyt c), and triggering a cascade leading to cell death.
Recently, Shi et al. [65] have described the development of a new tumor-specific and multi-activatable drug called nano-riceball that can be used in SDT. This is a multilayer micelle with a size of 96.8 nm, the core of which is constructed of amphipathic bottlebrushlike dextran-based polymer (DOS), which carries in its structure the anticancer drug DOX and pu18, as a potent ST. This construct is denoted as DDP. For specific tumor cell targeting, the upper layer of the DDP is covered by a bioengineered cell membrane [66], which carries the target motif of the Asn-Gly-Arg (NGR) peptide [67]. It is recognized by various isoforms of the CD13 receptor (aminopeptidase N), which occurs on the membrane of Figure 5. General principles of sonodynamic therapy. The action of ultrasound activates the sonosensitive agent and its transition to a higher energy state. When returning to the basic energy state, the energy generated is transformed in the form of heat, acoustic cavities, or light (sonoluminescence). As a result of these processes, reactive oxygen species (ROS) are formed, which leads to damage of the mitochondrial membrane, the release of cytochrome c (cyt c), and triggering a cascade leading to cell death.
However, some authors suggest that ST activation occurs differently due to sonoluminescence. Sonoluminescence is described as the emission of light that can occur when cavities collapse. This emitted light could thus activate the ST, similarly to that in PDT. However, scientists do not fully agree on this mechanism either [63]. It is, thus, likely that the mechanism of SDT action is a combination of several factors, which depend on the ST and the parameters of the ultrasound used. Although the exact mode of action of SDT has not been elucidated, SDT has tremendous potential in the treatment of cancers. An indisputable advantage of SDT over PDT is the deep penetration of ultrasound into soft tissues, which can be even more than 10 cm [64]. As some PSs can be used as STs, it is possible to combine both approaches as SDT-PDT.
Recently, Shi et al. [65] have described the development of a new tumor-specific and multi-activatable drug called nano-riceball that can be used in SDT. This is a multilayer micelle with a size of 96.8 nm, the core of which is constructed of amphipathic bottlebrushlike dextran-based polymer (DOS), which carries in its structure the anticancer drug DOX and pu18, as a potent ST. This construct is denoted as DDP. For specific tumor cell targeting, the upper layer of the DDP is covered by a bioengineered cell membrane [66], which carries the target motif of the Asn-Gly-Arg (NGR) peptide [67]. It is recognized by various isoforms of the CD13 receptor (aminopeptidase N), which occurs on the membrane of many types of tumor cells and, thus, it is a suitable target for the delivery of anticancer drugs ( Figure 6). In this way-targeted drug nano-riceball (NGR ® DDP) is preferentially captured on the surface of tumor cells, and is transported into the cells by endocytosis. Shi et al. [68] found that NGR ® DDP accumulates in HepG2 cells within 3 h of treatment. After sonication of the cells (0.56 W·cm −2 , 5 min), there is a rapid increase in ROS, lysosome disintegration, and collapse of the NGR@DDP structure. This leads to a partial release of DOX, then, additional DOX release is achieved by endogenous H 2 O 2 stimulation. By application of ultrasound, pu18 is also activated, which leads to further ROS generation. Due to the fluorescence of pu18, drug localization can be also monitored. Tests in nude mice with Luc-HepG2 tumors showed preferential accumulation of NGR ® DDP in tumor tissue as well as significant reduction or complete disappearance of the tumor after administration of NGR ® DDP in combination with an ultrasound. Besides, histological analysis showed extensive tumor tissue damage with minimal damage of normal/healthy tissues, thus suggesting high drug selectivity with the generation of minimal side effects.
OR PEER REVIEW 12 of 24 The ST drug PTPK has been developed to image and suppress the growth of pancreatic tumors [68]. Hydrophilic PTPK was prepared in the form of a linear chain composed of the cytotoxic peptide Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys (KLAKLAK), the ST pu18, and PEG, which is attached by a thiol bond. After PTPK treat- The ST drug PTPK has been developed to image and suppress the growth of pancreatic tumors [68]. Hydrophilic PTPK was prepared in the form of a linear chain composed of the cytotoxic peptide Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys (KLAK-LAK), the ST pu18, and PEG, which is attached by a thiol bond. After PTPK treatment with ultrasound, pu18 is activated to form singlet oxygen, which leads to cleavage of the thiol bond and cleavage of the PEG spacer. The rest of the SH-(pu18) KLAK molecule then forms self-assembled nanoparticles due to increased hydrophobicity. The nanoparticles are then transported into cells by endocytosis (Figure 7). Cytotoxicity assays on the Panc-1 cell line show that PTPK exhibits higher cytotoxicity and higher mitochondrial damage to treated cells after ultrasound treatment compared to non-cleavable PEG (pu18) KLAK and preprepared (pu18)-KLAK nanoparticles (without PEG). Using a multicellular tumor spheroid of Panc-1 cancer cells, the ability of single-stranded PTPKs to penetrate deeper into tissues was observed than with pre-packaged (pu18)-KLAK nanoparticles. In situ packaging of nanoparticles is also likely to lead to improved cell transport through endocytosis. Tests on nude mice implanted with Panc-1 cells have shown that PTPK in combination with ultrasound inhibits the growth of subcutaneous and orthotopic tumors.
The ST drug PTPK has been developed to image and suppress the growth of pancreatic tumors [68]. Hydrophilic PTPK was prepared in the form of a linear chain composed of the cytotoxic peptide Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys-Lys-Leu-Ala-Lys-Leu-Ala-Lys (KLAKLAK), the ST pu18, and PEG, which is attached by a thiol bond. After PTPK treatment with ultrasound, pu18 is activated to form singlet oxygen, which leads to cleavage of the thiol bond and cleavage of the PEG spacer. The rest of the SH-(pu18) KLAK molecule then forms self-assembled nanoparticles due to increased hydrophobicity. The nanoparticles are then transported into cells by endocytosis (Figure 7). Cytotoxicity assays on the Panc-1 cell line show that PTPK exhibits higher cytotoxicity and higher mitochondrial damage to treated cells after ultrasound treatment compared to non-cleavable PEG (pu18) KLAK and pre-prepared (pu18)-KLAK nanoparticles (without PEG). Using a multicellular tumor spheroid of Panc-1 cancer cells, the ability of single-stranded PTPKs to penetrate deeper into tissues was observed than with pre-packaged (pu18)-KLAK nanoparticles. In situ packaging of nanoparticles is also likely to lead to improved cell transport through endocytosis. Tests on nude mice implanted with Panc-1 cells have shown that PTPK in combination with ultrasound inhibits the growth of subcutaneous and orthotopic tumors. . Schematic representation of the ultrasound activatable polypeptide drug PTPK. The drug is applied to the bloodstream in a linear form, pu18 is activated to form singlet oxygen, which leads to cleavage of the thiol bond and disconnection of the PEG spacer. The rest of the molecule then consists of hydrophobic nanoparticles, which can more easily penetrate tumor cells.

Photoacoustic Imaging and Therapy
Photoacoustic imaging (PAI) is a promising technique for diagnostic and therapeutic purposes in the treatment of cancer due to its high resolution and deep penetration into tissues [69]. In medical applications, photoacoustic imaging is currently in clinical trials for imaging tumors of the breast [70,71], head and neck [72,73], thyroid gland [74], colon, and rectum [75]. The principle of PAI is the generation of acoustic ultrasonic waves based on the conversion of energy supplied by pulsed laser light. If a suitable molecule absorbs light energy, this energy is converted into heat, which also leads to an increase in the temperature around the molecule. Based on the thermoelastic expansion caused by the increase in temperature, ultrasonic waves are subsequently generated, recorded, and analyzed to form an image. Naturally occurring chromophores such as oxy-/deoxyhemoglobin, melanin, or exogenous inorganic and organic substances, which have the potential to absorb energy in the near-infrared region of the spectrum, are used as contrast agents in PAI. Endogenous chromophores can be used in a variety of applications, from brain mapping to monitoring angiogenesis and hypoxia, which are one of the main features of tumor presence. However, their main advantage, i.e., endogenous occurrence, is also their main limitation, due to the difficult distinction between the increased signal vs. the background signal (e.g., in tumor imaging). Some PSs, such as indocyanine green [76], and methylene blue [77] have been approved by the US Food and Drug Administration for application in PAI. Besides, due to absorption in long wavelengths, pu18 and its derivatives are also suitable for such application.
For example, it could be beneficial in distinguishing very small tumor features (<10 mm) from healthy tissues. PAI probes such as pu18/AHC⊂L (AHC⊂L-ammonium hydrogen carbonate encapsulated in liposomes) and CD44v6-pu18/AHC⊂L with improved photoacoustic properties are nanoparticles composed of a lipid bilayer, in which pu18 and NH 4 HCO 3 aggregates are incorporated [78]. NH 4 HCO 3 is in the hydrophilic core of the particle (pu18/AHC⊂L). After laser irradiation of the particles, pu18 aggregates are activated to produce heat and photoacoustic signals (Figure 8). The generated heat (42 • C) further initiates the slow decomposition of NH 4 HCO 3 , which leads to the formation of CO 2 bubbles, which significantly contribute to the long-term increase in the photoacoustic signal (8 h). For targeted imaging of bladder tumors, the surface of the nanoparticles was conjugated to an antibody against the surface protein CD44v6 (CD44v6-pu18/AHC⊂L). This protein has been identified in the colon [79,80], breast [81], and bladder [82] cancer cells, where it is produced to a greater extent than in healthy tissues. The CD44v6 protein is associated with cell migration, adhesion, and tumor metastasis. By comparing the effect of CD44v6-pu18/AHC⊂L on tumor and healthy human bladder tissue, a preferential accumulation of CD44v6-pu18/AHC⊂L was found in tumor tissue with a clear tumor delineation. Very small lesions (<5 mm) were also distinguished, which is a great advantage for early diagnosis of the tumor.
limitation, due to the difficult distinction between the increased signal vs. the background signal (e.g., in tumor imaging). Some PSs, such as indocyanine green [76], and methylene blue [77] have been approved by the US Food and Drug Administration for application in PAI. Besides, due to absorption in long wavelengths, pu18 and its derivatives are also suitable for such application.
For example, it could be beneficial in distinguishing very small tumor features (<10 mm) from healthy tissues. PAI probes such as pu18/AHC⊂L (AHC⊂L-ammonium hydrogen carbonate encapsulated in liposomes) and CD44v6-pu18/AHC⊂L with improved photoacoustic properties are nanoparticles composed of a lipid bilayer, in which pu18 and NH4HCO3 aggregates are incorporated [78]. NH4HCO3 is in the hydrophilic core of the particle (pu18/AHC⊂L). After laser irradiation of the particles, pu18 aggregates are activated to produce heat and photoacoustic signals (Figure 8). The generated heat (42 °C) further initiates the slow decomposition of NH4HCO3, which leads to the formation of CO2 bubbles, which significantly contribute to the long-term increase in the photoacoustic signal (8 h). For targeted imaging of bladder tumors, the surface of the nanoparticles was conjugated to an antibody against the surface protein CD44v6 (CD44v6-pu18/AHC⊂L). This protein has been identified in the colon [79,80], breast [81], and bladder [82] cancer cells, where it is produced to a greater extent than in healthy tissues. The CD44v6 protein is associated with cell migration, adhesion, and tumor metastasis. By comparing the effect of CD44v6-pu18/AHC⊂L on tumor and healthy human bladder tissue, a preferential accumulation of CD44v6-pu18/AHC⊂L was found in tumor tissue with a clear tumor delineation. Very small lesions (<5 mm) were also distinguished, which is a great advantage for early diagnosis of the tumor.  , in which aggregates of purpurin 18 (pu18) and NH 4 HCO 3 (in the hydrophilic core of the particle) are incorporated. Under the action of laser irradiation, the pu18 aggregates are activated to produce heat and a photoacoustic (PA) signal. The generated heat activates the slow decomposition of NH 4 HCO 3 , with the formation of CO 2 bubbles. This ensures a long-term increase in the PA signal, which can be easily detected for several hours [78].
The problem of the application of not only PAI drugs is bioavailability, which significantly affects the success of the whole process. An attractive approach of the preparation of new bioavailable drugs is the creation of so-called self-assembly molecules. These are usually multifunctional nanostructures that are formed based on van der Waals or electrostatic forces, hydrogen bonds, hydrophobic or π-π interactions directly in biological systems. This approach was used by Zhang et al. [26] to prepare self-assembled PAI nanofibers that are formed by precursor units. The precursor (pu18-PLGVRGRGD) is composed of pu18 as a PA functional molecule, the enzymatically cleavable peptide chain Pro-Leu-Gly-Val-Arg-Gly (PLGVRG), and the Arg-Gly-Asp (RGD) sequence targeting αvβ3 integrins as tumor cell surface structures. Under the action of the enzyme gelatinase, which occurs in tumor cells, the structure of pu18-PLGVRGRGD is cleaved. The remaining pu18-PLG units subsequently form nanofibers due to intramolecular π-π interactions ( Figure 9). Comparison of the effect of pu18-PLGVRGRGD with a pu18-PLGVRGRDG molecule (without target sequence) on αvβ3 overexpressing U87 cells integrates and gelatinizes, confirming the crucial role of the target motif in PA probe accumulation in tumor cells. In mice with implanted U87 cells, the PA signal increased already 2 h after pu18-PLGVRGRGD application. The highest PA signal was monitored 6 h after application and a stable PA signal could be observed for the next 24 h. Observed PA signal after application of pu18-PLGVRGRGD, range of double values compared to pu18-PLGVRGRDG (no target sequence), indicating increased accumulation of pu18-PLGVRGRGD in the tumor. The formation of nanofibers directly at the tumor site can also lead to a prolongation of the retention time of the probe in the tumor tissue (so-called assembly/aggregation-induced retention). The half-life of pu18-PLGVRGRGD is almost 24 h, which is six times more than in the case of the control probe pu18-PMGMRGRGD with a change in the peptide sequence that is not recognized by gelatinase (does not form nanofibers). In a long-term experiment with U87-xenografted mouse cells, complete tumor disappearance occurred after 23 days of treatment with the pu18-PLGVRGRGD probe in combination with laser treatment. The histopathological analysis did not prove damage to other organs (the heart, liver, kidneys, lungs), while the tumor tissue showed signs of necrosis. molecule (without target sequence) on αvβ3 overexpressing U87 cells integrates and gelatinizes, confirming the crucial role of the target motif in PA probe accumulation in tumor cells. In mice with implanted U87 cells, the PA signal increased already 2 h after pu18-PLGVRGRGD application. The highest PA signal was monitored 6 h after application and a stable PA signal could be observed for the next 24 h. Observed PA signal after application of pu18-PLGVRGRGD, range of double values compared to pu18-PLGVRGRDG (no target sequence), indicating increased accumulation of pu18-PLGVRGRGD in the tumor. The formation of nanofibers directly at the tumor site can also lead to a prolongation of the retention time of the probe in the tumor tissue (so-called assembly/aggregation-induced retention). The half-life of pu18-PLGVRGRGD is almost 24 h, which is six times more than in the case of the control probe pu18-PMGMRGRGD with a change in the peptide sequence that is not recognized by gelatinase (does not form nanofibers). In a longterm experiment with U87-xenografted mouse cells, complete tumor disappearance occurred after 23 days of treatment with the pu18-PLGVRGRGD probe in combination with laser treatment. The histopathological analysis did not prove damage to other organs (the heart, liver, kidneys, lungs), while the tumor tissue showed signs of necrosis. Figure 9. The scheme shows the structure of a prodrug (pu18-PLGVRGRGD) for the preparation of a targeted photoacoustic drug. The pu18-PLGVRGRGD precursor consists of purpurin 18 (pu18), Pro-Leu-Gly-Val-Arg-Gly (PLGVRG) as the enzyme-responsive peptide linker, and Arg-Gly-Asp (RGD) as the targeting ligand. Following application of the monomer precursor, it cleaves Figure 9. The scheme shows the structure of a prodrug (pu18-PLGVRGRGD) for the preparation of a targeted photoacoustic drug. The pu18-PLGVRGRGD precursor consists of purpurin 18 (pu18), Pro-Leu-Gly-Val-Arg-Gly (PLGVRG) as the enzyme-responsive peptide linker, and Arg-Gly-Asp (RGD) as the targeting ligand. Following application of the monomer precursor, it cleaves at the PLGVRG site in tumor cells. The remaining pu18-PLG units form nanofibers (NFs), which exhibit an enhanced photoacoustic signal [26].
The self-assembly of nanofibers from preformed nanoparticles directly inside cells was an approach used by Zhang et al. [83]. This study was based on the assumption that the formation of nanofibers is dependent on several factors such as concentration of the precursor, ionic strength, and temperature. A transformable polymer-peptide conjugate PKK-S-PEGm was created, which were composed of the cytotoxic peptide KLAKLAK that binds to the mitochondrial membrane, hydrogen-bonding peptide Lys-Leu-Val-Phe-Phe (KLVFF), glutathione-responsive motif disulfide bond linked to PEG chain, and photoacoustic/photothermal molecule pu18 [83]. PKK-S-PEG probes were prepared in the form of 40-nm nanoparticles, which are transported into cells by endocytosis. Upon entry inside the cells, disulfide bridges are cleaved by glutathione, thereby removing the PEG chain stabilizing the spherical structure of the nanoparticle. The nanoparticles are then gradually transformed into nanofibers, which are formed owing to the hydrogen bonds of the KLVFF motif. The morphological change of nanoparticles into nanofibers can be accelerated by laser photoactivation of the particles. Due to the presence of pu18, heat is generated after laser illumination, which accelerates the transformation of nanoparticles into nanofibers up to four times ( Figure 10). Cytotoxicity assays on the HeLa, MCF-7, and L929 cell lines showed increased cytotoxicity and higher number of apoptotic cells treated with PKK-S-PEG in combination with laser illumination than in non-illuminated cells. Due to the assay on BALB/c mice transplanted with Hela cells, increased accumulation and retention time of the drug in the tumor tissue was observed. Due to the formation of photoacoustic waves, it was possible to monitor the formation of nanofibers and the movement of the drug in real-time.
stabilizing the spherical structure of the nanoparticle. The nanoparticles are then gradually transformed into nanofibers, which are formed owing to the hydrogen bonds of the KLVFF motif. The morphological change of nanoparticles into nanofibers can be accelerated by laser photoactivation of the particles. Due to the presence of pu18, heat is generated after laser illumination, which accelerates the transformation of nanoparticles into nanofibers up to four times ( Figure 10). Cytotoxicity assays on the HeLa, MCF-7, and L929 cell lines showed increased cytotoxicity and higher number of apoptotic cells treated with PKK-S-PEG in combination with laser illumination than in non-illuminated cells. Due to the assay on BALB/c mice transplanted with Hela cells, increased accumulation and retention time of the drug in the tumor tissue was observed. Due to the formation of photoacoustic waves, it was possible to monitor the formation of nanofibers and the movement of the drug in real-time. Figure 10. The diagram shows the chemical structure of the polymer-peptide conjugate PKK-S-PEG. It is composed of the cytotoxic peptide Lys-Leu-Ala-Lys-Lu-Ala-Lys (KLAKLAK), which binds to the mitochondrial membrane, a hydrogen-bonding peptide motif Lys-Leu-Val-Phe-Phe (KLVFF, originated from the Aβ protein), the hydrophobic unit of poly(ethylene glycol) = PEG, which is attached via a disulfide bridge, and the photoacoustic/photothermal molecule pu18. Drug monomers are spontaneously packaged into nanoparticles, which are transported into cells by endocytosis. Upon entering the cells, the PEG chain is cleaved leading to the spontaneous transformation of nanoparticles (NPs) into mitochondrially targeted nanofibers (NFs). The conversion in NFs can be accelerated photothermally [83].
A similar approach was used by Zhou et al. [25], who studied the properties of selfassembly of molecules composed of pu18 and the amino acid arginine to monitor the aggregation process by PAI in vivo [25]. The prepared derivatives PA1, PA3, and PA7 differed from each other in the number of arginine units (1, 3, 7), from which the spectral Figure 10. The diagram shows the chemical structure of the polymer-peptide conjugate PKK-S-PEG. It is composed of the cytotoxic peptide Lys-Leu-Ala-Lys-Lu-Ala-Lys (KLAKLAK), which binds to the mitochondrial membrane, a hydrogenbonding peptide motif Lys-Leu-Val-Phe-Phe (KLVFF, originated from the Aβ protein), the hydrophobic unit of poly(ethylene glycol) = PEG, which is attached via a disulfide bridge, and the photoacoustic/photothermal molecule pu18. Drug monomers are spontaneously packaged into nanoparticles, which are transported into cells by endocytosis. Upon entering the cells, the PEG chain is cleaved leading to the spontaneous transformation of nanoparticles (NPs) into mitochondrially targeted nanofibers (NFs). The conversion in NFs can be accelerated photothermally [83].
A similar approach was used by Zhou et al. [25], who studied the properties of selfassembly of molecules composed of pu18 and the amino acid arginine to monitor the aggregation process by PAI in vivo [25]. The prepared derivatives PA1, PA3, and PA7 differed from each other in the number of arginine units (1, 3, 7), from which the spectral properties, the ability to form aggregates, and the morphology of the formed particles are derived. In the case of monomeric pu18, there was a redshift of the Q y band from 700 to 750 nm during the aggregation process, which indicates the formation of J-type aggregates. At the same time, the fluorescence signal gradually decreased. In the case of monomers PA1, PA3, and PA7, the extinction coefficients (at 700 nm, in dimethylsulfoxide) increased at the same concentration together with the increasing number of arginine units. In an aqueous environment, where conjugates aggregated, higher solubility was observed with a higher number of arginine units leading to less redshift due to hydrophobicity and positive charge of the conjugates. With a higher number of arginine units, a reduced ability to form aggregates and a weak π-π interaction were also observed for PA7. The same result was shown by the measurement of the fluorescence intensity; in the case of PA1, there was a complete loss of fluorescence, which indicates that all monomers undergo to an aggregated state. In contrast, PA7 showed a similar level of fluorescence in the aqueous medium as in the monomeric state. The fluorescence intensity of PA3 was reduced in the aqueous medium, but it was not completely lost. In aqueous media, both PA3 and PA7 are likely to occur in both monomeric and aggregated states. On the contrary, it is known that as the fluorescence signal decreases, the PA signal increases. In connection with the photoacoustic signal, the heat conversion efficiency of the conjugates was studied. A 3-fold increase in heat conversion efficiency was observed for the PA1 and PA3 aggregates compared to their monomeric state. An increase in heat conversion efficiency was also observed for PA7, although not to such an extent. The degree of aggregation of the conjugates in the aqueous medium correlated with heat conversion efficiency, which is proportional to the photoacoustic signal. Zhou et al. [25] also defined the relationship between the degree of aggregation and the relative photoacoustic ratio as a useful tool for aggregation research.
RGD-Dex/NPBA-pu18 (RDNP) monomers were generated to monitor targeted drug delivery, and the structural changes induced by the acidic environment of the cells. By different molar ratios of biocompatible peptide Cys-Gly-Gly-Arg-Gly-Asp (RGD) with dextran (RGD-Dex) as a carrier and a photoacoustic probe pu18 modified with boric acid (NPBA-pu18), a total of five types of monomers (P1-P5) with different properties were prepared. It was found that when NPBA-pu18 is in a 3-fold and higher molar excess over RGD-Dex, RDNP monomers in an aqueous medium can be self-assembled into nanoparticles [84]. The hydrophobic NPBA-pu18 forms a core of nanoparticles that is surrounded by a hydrophilic RGD-Dex. It serves to stabilize the nanoparticle. In an acidic environment, RDNP may cleave due to a pH-dependent phenyl borate bond. The released NPBA-pu18 can repackage into the structure of highly organized nanofibers due to high hydrophobicity and π-π interactions ( Figure 11). After laser irradiation, it is then possible to monitor the PA signal and distinguish the structural changes that are characteristic for the monomeric and aggregated state of NPBA-pu18. P2 (single-stranded) and P5 (nanogranulated) labeled with Cy5 were used for cell entry assays in HeLa cells. Based on the intensity of the fluorescent signal, it was determined that P5 internalized into cells more efficiently than P2 by caveolae-mediated and clathrin-mediated endocytosis. Both conjugates were localized in cell lysosomes/endosomes. 1h after the treatment of HeLa cells with P5, an increasing photoacoustic signal was detected and after 3 h when all nanoparticles were likely to dissociate to form NPBA-pu18 aggregates, a stable PA signal was achieved. The entire process of structural transformation of RDNP was monitored in real-time using PAI, which makes this method an important tool for following many cell processes, such as targeted drug delivery or autophagy, which is often connected to cancer.
In general, autophagy is a natural catabolic process, in which proteins, organelles, and other cell components are degraded. It is one of the essential cellular processes for maintaining homeostasis, which occurs in response to stressful conditions such as hypoxia, presence of ROS, or lack of nutrients. Some drugs, such as DOX, have been reported to up-regulate autophagy, which can, however, paradoxically lead also to resistance of the cell to chemotherapy [85,86]. Therefore, autophagy inhibitors are commonly co-administered with chemotherapeutics to help increase the success of anticancer therapy [87]. However, the combination of these drugs often leads to high systemic toxicity and damage to the organism. Thus, preventive monitoring of autophagy in real time, directly in tumor cells using PAI, could be beneficial. With this goal, Lin et al. [88] developed a novel photoacoustic in vivo self-assembled probe (DDP18, Figure 12). It is composed of hydrophobic pu18 as a signaling molecule, Gly-Lys-Gly-Ser-Phe-Gly-Phe-Thr-Gly (GKGSFGFTG) peptide, the cleavage site of autophagy-related cysteine protease, and poly(amidoamine) dendrimer, which serves as a carrier increasing the solubility and biocompatibility of the molecule. Upon entry of the probe into cells undergoing autophagy, the pu18 residue is enzymatically cleaved with a linker to aid in its folding.
PEER REVIEW 17 of 24 Figure 11. The diagram shows the structure of the photoacoustic drug RDNP. The drug monomers consist of dextran that serves as a carrier, a biocompatible peptide Cys-Gly-Gly-Arg-Gly-Asp (RGD), and a photoacoustic probe pu18, which is modified with boric acid. RDNP monomers spontaneously form nanoparticles (NPs) in an aqueous environment, which can be cleaved to form highly organized nanofibers (NFs) upon transition to the acidic environment of tumor cells. The conversion of NPs to NFs can be monitored in real-time using photoacoustic imaging [84].
In general, autophagy is a natural catabolic process, in which proteins, organelles, and other cell components are degraded. It is one of the essential cellular processes for maintaining homeostasis, which occurs in response to stressful conditions such as hypoxia, presence of ROS, or lack of nutrients. Some drugs, such as DOX, have been reported to up-regulate autophagy, which can, however, paradoxically lead also to resistance of the cell to chemotherapy [85,86]. Therefore, autophagy inhibitors are commonly co-administered with chemotherapeutics to help increase the success of anticancer therapy [87]. However, the combination of these drugs often leads to high systemic toxicity and damage to the organism. Thus, preventive monitoring of autophagy in real time, directly in tumor cells using PAI, could be beneficial. With this goal, Lin et al. [88] developed a novel photoacoustic in vivo self-assembled probe (DDP18, Figure 12). It is composed of hydrophobic pu18 as a signaling molecule, Gly-Lys-Gly-Ser-Phe-Gly-Phe-Thr-Gly (GKGS-FGFTG) peptide, the cleavage site of autophagy-related cysteine protease, and poly(amidoamine) dendrimer, which serves as a carrier increasing the solubility and biocompatibility of the molecule. Upon entry of the probe into cells undergoing autophagy, the pu18 residue is enzymatically cleaved with a linker to aid in its folding.
It has been reported that pu18 in the form of aggregates/nanostructures has a higher photoacoustic response after laser activation than free pu18 due to a change in photothermal conversion capacity [78,89]. Simultaneously with the increase in the PA signal, a decrease in pu18 fluorescence was observed. When verifying the cytotoxic effects in the MCF-7 cell line, very low cytotoxicity was found both without and after laser treatment of the cells under conditions corresponding to PAI (735 nm, 100 mW, 10 s), the rate of the photoacoustic signal was also very low (autophagy was not detected). When cells treated with DPP18 were simultaneously treated with an autophagy inducer, a significant increase in photoacoustic signal was measured after laser irradiation. Using DPP18 in vivo Figure 11. The diagram shows the structure of the photoacoustic drug RDNP. The drug monomers consist of dextran that serves as a carrier, a biocompatible peptide Cys-Gly-Gly-Arg-Gly-Asp (RGD), and a photoacoustic probe pu18, which is modified with boric acid. RDNP monomers spontaneously form nanoparticles (NPs) in an aqueous environment, which can be cleaved to form highly organized nanofibers (NFs) upon transition to the acidic environment of tumor cells. The conversion of NPs to NFs can be monitored in real-time using photoacoustic imaging [84].

Photothermal Therapy
The basic component of PTT is, as in the case of PDT, a photosensitive drug molecule that is activated by laser light, usually at near-infrared wavelengths. PTT, however, converts light energy absorbed by a photosensitive drug into thermal energy, which can heat the target tissue to more than 43 °C, leading to DNA damage, denaturation of proteins, and subsequent apoptosis or necrosis. The type of cell death depends on the drug and the type of laser irradiation (laser energy, number of pulses, duration of irradiation) used. As PTT does not require the presence of oxygen in the tissues, it is also suitable for hypoxic tumors, which are often resistant to classical therapy [90]. Nanoparticles of inorganic origin are often used as PTT drugs, including porphyrins, which are usually modified into a nanoparticle structure. However, due to the similarity of PTT and PDT, it is possible to often come across combined drugs that utilize properties of both PTT and PDT to increase Figure 12. Chemical structure of photoacoustic in vivo self-assembled nanoprobes for imaging and quantitative detection of autophagy. The molecule is composed of poly (amidoamine) dendrimers (PAMAM), the specifically cleavable peptide Gly-Lys-Gly-Ser-Phe-Gly-Phe-Thr-Gly (GKGSFGFTG), and purpurin 18 (pu18) [88].
It has been reported that pu18 in the form of aggregates/nanostructures has a higher photoacoustic response after laser activation than free pu18 due to a change in photothermal conversion capacity [78,89]. Simultaneously with the increase in the PA signal, a decrease in pu18 fluorescence was observed. When verifying the cytotoxic effects in the MCF-7 cell line, very low cytotoxicity was found both without and after laser treatment of the cells under conditions corresponding to PAI (735 nm, 100 mW, 10 s), the rate of the photoacoustic signal was also very low (autophagy was not detected). When cells treated with DPP18 were simultaneously treated with an autophagy inducer, a significant increase in photoacoustic signal was measured after laser irradiation. Using DPP18 in vivo in mice, it has been shown that monitoring tumor autophagy with PAI can be successfully used to optimize the dosing schedule of the chemotherapeutic DOX in combination with the autophagy inhibitor hydroxychloroquine. Mice treated with the adjusted dosing regimen showed similar tumor growth suppression as mice treated with the traditional dosing regimen. Besides, however, no significant weight loss of the mice or a decrease in white blood cell and platelet counts were observed with the adjusted dose, suggesting an overall better physical condition of the animals. The use of PAI can thus be a promising tool for personalized medicine.

Photothermal Therapy
The basic component of PTT is, as in the case of PDT, a photosensitive drug molecule that is activated by laser light, usually at near-infrared wavelengths. PTT, however, converts light energy absorbed by a photosensitive drug into thermal energy, which can heat the target tissue to more than 43 • C, leading to DNA damage, denaturation of proteins, and subsequent apoptosis or necrosis. The type of cell death depends on the drug and the type of laser irradiation (laser energy, number of pulses, duration of irradiation) used. As PTT does not require the presence of oxygen in the tissues, it is also suitable for hypoxic tumors, which are often resistant to classical therapy [90]. Nanoparticles of inorganic origin are often used as PTT drugs, including porphyrins, which are usually modified into a nanoparticle structure. However, due to the similarity of PTT and PDT, it is possible to often come across combined drugs that utilize properties of both PTT and PDT to increase the antitumor efficacy. Kim et al. [91] prepared a complex of combined PTT/PDT gold-nanorods (GNR-PS). The formulation is based on GNR composed of hydrogen tetrachloroaurate (III) trihydrate (HAuCl 4 ·3H 2 O) and cetyltrimethylammonium bromide, which is, however, cytotoxic. For this reason, the layer-by-layer method was used to prepare GNR-PS using cationic poly (allylamine hydrochloride), which suppresses the cytotoxicity of cetyltrimethylammonium bromide and is important for the formation of a dual PTT/PDT system using pu18 as a PS. Verification of the PTT and PDT effects of the GNR-PS drug was performed in A549 cells. After the cell treatment with the GNR-PS, they were photoactivated with a laser (808 nm, 120 J·cm −2 , 1 min) for PTT induction followed by a halogen PDT-inducing lamp (a band-pass filter 640-710 nm, 2 J·cm −2 , 15 min). PTT/PDT-treated cells showed the highest decrease in viability (39% of viable cells) compared to single therapies (PDT = 90%, PTT = 73% of viable cells). At the same time, no toxicity of GNR-PS without illumination was observed in the evaluated concentration range (1-20 µM). The results also showed that within 1 min after the PTT, 57% of the pu18 contained in the GNR-PS was released and without photoactivation only 2% within 60 min. The combined GNR-PS drug effectively utilizes the synergistic effect of PTT/PDT and is a potent antitumor drug.

Phototeranostic
The aforementioned methods might all be combined. Moreover, it is possible to combine them with diagnostic tools, which is clinically a very interesting and more and more emerging approach, generally called theranostics. Theranostics represents therapy and diagnosis of a disease covered by a single substance or particle, which, in general, can exhibit very diverse biological activities. The therapeutical part may consist of all possible currently known chemotherapeutics, the structure of which can be modified and linked to the diagnostic part. Diagnosis, in this case, is provided usually by radioactivity or fluorescence of the particular substance. Nevertheless, also other clinical diagnostic tools are being involved, such as magnetic resonance, computer tomography, and others [92]. Pu18 and related derivatives are also being developed for such applications. The advantage of pu18 is the ability to absorb light and emit fluorescence. Once delivered into pathological cells, this ability can be utilized for tumor imaging. Zhang et al. 2018 synthesized pHdependent pu18 loaded GO particles, which were stable at physiological pH, and at low pH, often occurring in tumors, released free pu18. This might be detected by increased fluorescence and, thus, display the tumor. Such particles have also a better ability to yield singlet oxygen (62.6% quantum yield) compared to free pu18 (58.82%). In HepG2 cells, IC 50 of GO-pu18 after 10 min of irradiation was 1.39 ± 0.38 µg·mL −1 , whereas that of free pu18 was 5.3 ± 0.79 µg·mL −1 . The viability of cells without irradiation was higher than 90% for all the studied concentrations [39]. Generally, pu18 has cytotoxic and fluorescent properties, which makes this compound alone a theranostics agent. Thus, the only question is, how to efficiently and specifically deliver this substance to cancer cells and how to preserve its fluorescent and phototoxic properties. The answer might be again proper derivatization. Sun et al. [93] developed a theranostic system consisting of self-assembled nanoparticles (ppu18-lipos) of lipid-pu18 of 2 mol% and 65 mol% concentrations and pure lipids. The lipid-pu18 derivatives were created by the reaction of pu18 and 1-palmitoyl-2-hydroxy-snglycero-3-phosphocholine. Ppu18-lipos enabled trimodal in vivo imaging by fluorescent and photoacoustic methods and magnetic resonance ( Figure 13). The fluorescent signal was observed in vitro more after low-density particle treatment because pu18 in higher concentrations formed aggregates, which caused fluorescence quenching. Photoacoustic signals, on the contrary, increase linearly with pu18-lipid concentrations, since such signals correlate with the thermal expansion of laser irradiated materials. Magnetic resonance signal, which was enabled by treatment with ppu18-lipos-Mn 2+ chelates, also increased with ppu18 concentration. A potent therapeutic effect of the ppu18-lipos particles was achieved by PDT and PTT in combination and, also, activation of the immune response was detected after laser irradiation. The synergism of PDT and PTT was followed in vivo in mice bearing 4T1 breast tumors. Astonishing 90% inhibition of tumor growth was achieved with a concentration of ppu18, which was 6 mg·kg −1 lower than that for PDT and PTT alone. Importantly, the advantageous layout of the experiment seems to be a pretreatment of low-density particles and laser activation, because PDT ensures more facile endocytosis of further pu18-lipid particles and subsequently more efficient PTT [93].
for all the studied concentrations [39]. Generally, pu18 has cytotoxic and fluorescent properties, which makes this compound alone a theranostics agent. Thus, the only question is, how to efficiently and specifically deliver this substance to cancer cells and how to preserve its fluorescent and phototoxic properties. The answer might be again proper derivatization. Sun et al. [93] developed a theranostic system consisting of self-assembled nanoparticles (ppu18-lipos) of lipid-pu18 of 2 mol% and 65 mol% concentrations and pure lipids. The lipid-pu18 derivatives were created by the reaction of pu18 and 1-palmitoyl-2hydroxy-sn-glycero-3-phosphocholine. Ppu18-lipos enabled trimodal in vivo imaging by fluorescent and photoacoustic methods and magnetic resonance ( Figure 13). The fluorescent signal was observed in vitro more after low-density particle treatment because pu18 in higher concentrations formed aggregates, which caused fluorescence quenching. Photoacoustic signals, on the contrary, increase linearly with pu18-lipid concentrations, since such signals correlate with the thermal expansion of laser irradiated materials. Magnetic resonance signal, which was enabled by treatment with ppu18-lipos-Mn 2+ chelates, also increased with ppu18 concentration. A potent therapeutic effect of the ppu18-lipos particles was achieved by PDT and PTT in combination and, also, activation of the immune response was detected after laser irradiation. The synergism of PDT and PTT was followed in vivo in mice bearing 4T1 breast tumors. Astonishing 90% inhibition of tumor growth was achieved with a concentration of ppu18, which was 6 mg·kg −1 lower than that for PDT and PTT alone. Importantly, the advantageous layout of the experiment seems to be a pretreatment of low-density particles and laser activation, because PDT ensures more facile endocytosis of further pu18-lipid particles and subsequently more efficient PTT [93]. Figure 13. The diagram shows the structure of a combined photodynamic/photothermal drug, which is composed of purpurin 18 (pu18), a hydrophobic part formed by C-16 acyl, and a hydrophilic choline unit. Ppu18-lipid drug monomers form self-assembled liposomes, which can be used as combined theranostics for PDT/fluorescence imaging or PTT/photoacoustic imaging, depending on the amount of pu18 used (mol%) [93]. Figure 13. The diagram shows the structure of a combined photodynamic/photothermal drug, which is composed of purpurin 18 (pu18), a hydrophobic part formed by C-16 acyl, and a hydrophilic choline unit. Ppu18-lipid drug monomers form self-assembled liposomes, which can be used as combined theranostics for PDT/fluorescence imaging or PTT/photoacoustic imaging, depending on the amount of pu18 used (mol%) [93].

Conclusions
Chlorophyll and its natural metabolites are a very valuable tool in the development of novel anticancer drugs. In particular, one of its metabolites pu18 is a very potent multifunctional molecule that can be used in several anticancer therapies such as PDT, SDT, and PTT, but also in theranostics and tumor imaging for their early diagnosis, e.g., by PAI. All these applications are possible due to the structure of pu18, which allows strong energy absorption and further transfers of this energy leading to the creation of cytotoxic ROS, heat, or fluorescent signal. Another great advantage of pu18 is its low systemic toxicity in the dark environment, thus, causing low side effects during the therapy. Unfortunately, further advancement into clinics is hampered by its low water solubility. However, this problem can be easily overcome by its derivatization, which leads to the synthesis of many potent conjugates. Owing to its facile derivatization and unique properties, pu18 represents an effective tool for the development of novel PSs and multimodal drugs, which seem to be the future of anticancer therapy.