Near-infrared light-activated membrane fusion for cancer cell therapeutic applications

A NIR light activatable membrane fusion method was developed for cancer cell therapeutic applications.


Introduction
The development of articial cell-mimicking compartments, e.g., articial cells is a holy-grail challenge in the rapidly developing area of "systems chemistry". 1-3 Different self-organized micro/nanostructures such as liposomes, 4-7 polymersomes, [8][9][10] aqueous microdroplets, 11 dendrosomes, 12,13 and microcapsules 14,15 were introduced as biomimetic cell structures. By the incorporation of loads into cell-mimicking compartments, cell-like functions such as controlled catalysis and biocatalysis in these compartments were demonstrated. 16,17 In addition, the incorporation of stimuli-responsive elements into the boundaries of "articial cells" allowed the triggered release of loads across the cell-like interfaces. 18,19 Different triggers, such as temperature, 20 light, 21,22 pH, [23][24][25] redox reagents, 26 magnetic elds 27 and ultrasound, 28 were applied to induce the release of the loads from articial cells. The inter-cell interactions and, particularly, cell-cell fusion represent important processes in biological systems such as neurotransmission 29,30 exo-and endocytosis, 31 signal transduction [32][33][34][35] and viral infection. 36,37 For example, soluble N-ethylmaleimidesensitive-factor attachment receptors (SNAREs) represent a broad class of proteins and protein subunits that induce membrane fusion. [38][39][40] Not surprisingly, substantial research efforts are directed towards the development of fusion pathways of cell-like compartments, e.g., liposomes, as biomimetic model systems. 41,42 In this context, the intrinsic recognition of complementary nucleic acids or peptide nucleic acids provides a versatile means to interconnect liposomes and induce liposome-liposome fusion. [43][44][45] For example, lipidated or cholesterol-modied complementary nucleic acids incorporated into the boundaries of two different kinds of liposomes allowed the inter-hybridization of liposomes and their fusion. [46][47][48][49] Nonetheless, these fusion processes were not triggered by auxiliary stimuli, thus eliminating spatiotemporal fusion events. The fusion efficiency of the liposomes was affected by the geometries and duplex lengths of the bridging nucleic acids. [50][51][52] Also, the SNARE-mediated fusion of phospholipid vesicles was enhanced by lipidated nucleic acid tethers. 53 In addition, the pH-induced triple-stranded assembly of lipidated peptides and the formation of ion-complexes of boronate ester bridges using appropriate lipidated ligands were demonstrated. 54 Different applications of the fusion of liposomes were suggested and they include the detection of miRNAs by nucleic acid-mediated fusion of liposomes 55 or the miRNA-induced inhibition of the nucleic acid-functionalized liposomes, 56 and the barcoding of bioreactions through dictated fusion of vesicles. 33,57,58 In addition, liposome-membrane fusion processes were suggested for drug release applications. 59,60 While impressive progress in the understanding of the fusion process of liposomes was made, there are several difficulties underlying the processes. While interconnection of liposomes, via the different mechanisms, is obvious, the evaluation of the yield of the full fusion of the two liposomes that form an enlarged liposome, demonstrating the exchange of loads present in the two parent liposome compartments, is important. Different physical means to follow the interconnection and full fusion of liposomes, e.g., dynamic light scattering (DLS), 61,62 surface plasmon resonance (SPR), 63,64 and photophysical methods to quantitatively analyze the fusion process by following the FRET or uorescence properties of the contents in the fused structures, were introduced. 65, 66 The fusion of liposomes provides the basic principle for the fusion of liposomes with the cell membrane and the incorporation of loads into the cell cytoplasm. Indeed, nucleic acid-modied liposomes could be fused with lipidated-or cholesterol-functionalized cells, resulting in the delivery of the liposomal loads into the cells. 48 Such liposome-cell fusion processes could be an indispensable pathway for nanomedicine by providing means to introduce drugs into cells and, particularly, anti-cancer drugs into cancer cells. 59 The spatiotemporal control over the fusion of cells plays an important role in biological systems (selective and vectorial targeted fusion of cells in space, and time-dominated fusion of cell membranes). While substantial progress in the development of spontaneous fusion of liposome mixtures modied with complementary recognition elements was achieved, the examples of spatiotemporal control over the fusion of liposomes are scarce. The development of such systems would require the incorporation of: (i) a stimuli-responsive unit into the fusion element which enables the time-and space-triggered activation of the fusion process. (ii) A targeting unit coupled to the fusion element which dictates spatial, vectorial and selective fusion of the membranes. In fact, the development of a controlled spatiotemporal membrane fusion process for controlled and triggered release of drugs into target cells, could be important for cancer therapy. 48 An impressive example for temporal control over membrane fusion has been demonstrated by the preparation of two oppositely loaded liposomes charged with coiled-coil polyethylene glycolated E and K SNARE peptides, where one of the peptide-modied liposomes was shielded with a lipidated photolabile o-nitrobenzyl ester polyethylene glycol chain. 67 While the shielding of the peptide promoter unit prohibited fusion, the UV light-induced cleavage of the photoprotecting units and the sequestered removal of the polyethylene glycol shielding tethers stimulated the temporal fusion of the membranes. The system introduced a principle for temporal membrane fusion, but it lacks the spatial control of membrane fusion. In addition, the use of UV light to deprotect the shielding units is a major disadvantage for future medical applications.
The base sequence encoded in nucleic acids provides, however, a rich "tool-box" for designing spatiotemporal membrane fusion processes. Beyond the use of nucleic acid complementarity (duplex formation) as a membrane fusion principle, one may introduce into the fusing counter-parts stimuli-responsive triggering units and/or targeting units to yield spatiotemporal membrane fusion processes. This includes the possible application of sequence-specic aptamers that target liposomes to specic cell receptors, 68,69 and the use of different switchable, signal-triggered recongurable nucleic acid structures, by using triggers such as photoisomerizable intercalators, 70 triplex, 71 metal-ions bridged duplex 72 and redox agents-functionalized nucleic acids. 73 One particular functionality that was previously used to activate nucleic acid structures includes o-nitrobenzyl phosphate photoprotecting groups. 74 For example, photochemical patterned deprotection of the o-nitrobenzyl phosphate monolayer followed by the hybridization chain reaction was used to generate DNA branched polymer patterns on surfaces. [75][76][77] Also, o-nitrobenzyl phosphate nucleic acid-based drug-loaded microcapsules were used as functional carriers for the light-induced release of drugs. 21 In addition, onitrobenzyl phosphate-modied DNA probes were used as lightactivated functional structures for the optical or electrochemical sensing of miRNAs. 78 In the present study we introduce different o-nitrobenzyl phosphate-protected nucleic acids as functional units that induce liposome-liposome and liposome-cell fusion processes. Besides the characterization of the different membrane fusion congurations, we address the application of the fusion of drug (doxorubicin)-loaded photo-responsive liposomes with cancer cells as a means to stimulate targeted spatiotemporal cytotoxicity towards cancer cells. The main achievements of the present study include: (i) the photo-responsive liposomes are loaded with upconversion nanoparticles (UCNPs). 79 This allows the light-induced deprotection of the photolabile protecting groups, and the fusion of the different membrane systems, by near IR irradiation (l ¼ 980 nm). The UCNPs yield a localized 365 nm light source for the deprotection processes. It should be noted that the conventional light-induced deprotection of the onitrobenzyl phosphate groups requires harmful UV light (l ¼ 365 nm) as the light source. The NIR irradiation of the UCNPloaded liposomes provides a means to generate UV light locally without damaging neighboring normal cells. (ii) In addition, we integrate aptamers as functional units to target the liposome to specic membrane receptors, thereby leading to the spatiotemporal control over liposome-membrane fusion. It should be noted that previous studies have demonstrated the targeting of antibody-modied upconversion nanoparticle macrophage membranes 80 and antibody-modied upconversion particles were applied to image tumor cells 81 and to stimulate the photochemical generation of reactive oxygen species for photodynamic cancer cell therapy. 82 Nonetheless, in all of these studies, upconversion nanoparticles were applied as uorescent labels or intracellular catalysts yet not used as active membrane-membrane or membrane-cell fusion promoters. The present study introduces new principles to apply integrated upconversion nanoparticles in liposomes carrying drugs or optical labels as vehicles to actively induce membranemembrane and membrane-cell fusion accompanied by the controlled release of imaging agents and drugs.

Results and discussion
The near-infrared light-induced fusion of two liposomes is shown in Fig. 1. One type of liposomes, L 1 , is functionalized with 3 0 -cholesterol-tethered hairpin nucleic acid (1) units that are modied with o-nitrobenzylphosphate photoreactive bridging groups. The liposomes were loaded with upconversion nanoparticles (UCNPs) capable of converting near-infrared light (NIR) into UV light. In addition, the liposomes L 1 were loaded with Tb 3+ ions. The second type of liposomes L 2 were functionalized at their boundaries with the 5 0 -cholesterol-modied nucleic acid (2). The (2)-functionalized liposomes were loaded with 2,6-pyridinedicarboxylic acid, DPA. The o-nitrobenzylphosphate bridging units stabilize the caged hairpin structure (1). The UV irradiation of the photoprotective groups, l ¼ 365 nm, leads to the cleavage of the o-nitrobenzyl phosphate units into o-nitrosobenzylphenone functionalities and to the fragmentation of the hairpin structure, resulting in the (1 0 /1 00 )-modied liposome L 0 1 (see Fig. S2, ESI †). As the liposomes L 1 are loaded with the UCNPs, the NIR irradiation of the UCNPs, l ¼ 980 nm, leads to effective localized UV luminescence at 365 nm, resulting in the unlocking of the hairpin units associated with the liposomes L 1 to L 0 1 . As the (1 0 /1 00 )-functionalized liposomes L 0 1 include nucleic acid tethers complementary to the (2)-tethered liposomes, the formation of (1 0 /2) duplex bridged liposomes is anticipated to allow their fusion. The fusion process results in the exchange of the loads between the two liposome compartments, and thus, the fusion-guided exchange of the loads yields then the Tb 3+ -DPA uorescent complex. Accordingly, the time-dependent uorescence changes, in the L 1 /L 2 mixture, upon the light induced uncaging of L 1 , and the timedependent size changes (evaluated by light scattering) provide two physical means to probe the dynamics of fusion of the liposomes and to evaluate the yield of the full fusion of the liposome compartments leading to exchange of loads.
The photostimulated fusion process of the liposomes L 1 and L 2 was developed following several steps: (i) in the rst (1 0 /1 00 ),-modied Tb 3+ -ion loaded liposomes and (2)-functionalized liposomes were prepared. Their mixture led to the fusion of the liposomes as evidenced by the time-dependent uorescence changes and size changes of the fused liposomes, Fig. S1. † These experiments validated that the dynamic fusion process can be probed by the uorescence change, upon formation of the Tb 3+ -DPA complexes and by the size changes accompanying the fusion process using dynamic light scattering experiments (see Fig. S1 and accompanying discussion †). (ii) In the second step, the photoresponsive (1)-functionalized liposomes L 1 loaded with Tb 3+ , in the absence of UCNPs, were mixed with the (2)-modied liposomes. No fusion of the liposomes could be detected without UV light. The irradiation of the mixture with UV light, l ¼ 365 nm, induced the photodeprotection of the o-nitrobenzylphosphate units, the fragmentation of the hairpin units (1) and the formation of the (1 0 / 1 00 )-functionalized liposomes L 0 1 that fused with liposomes L 2 by the formation of inter-liposome (1 0 /2) duplexes, Fig. S2(A). † This is evident by the increase in the liposome sizes from ca. 250 nm diameter to ca. 300 nm sized liposomes, Fig. S2(B), † and by the time dependent increase in the uorescence of the Tb 3+ -DPA complex generated upon the mixing of the loads associated with L 0 1 and L 2 upon fusion, Fig. S2(C). † (iii) In the third step, the integrated NIR-induced fusion of the liposomes, L 1 /L 2 , was examined, Fig. 1. In this system, the UCNPs were co-loaded with Tb 3+ ions and the liposome mixture of L 1 and L 2 was irradiated with NIR light, l ¼ 980 nm. Under these conditions, the luminescence of the UCNPs yields localized UV light in the conned environment of L 1 . Under these conditions, the localized UV light cleaves the hairpin units (1), leading to the (1 0 )-functionalized liposomes, L 0 1 , that fuse with liposomes L 2 , Fig. 1(A). The time-dependent size changes of the liposomes upon irradiation of the liposome mixture with NIR light are presented in Fig. 1(B). The resulting fused liposomes reveal an average diameter of 310 nm while the nonirradiated liposomes show an unchanged diameter of ca. 260 nm. Also, Fig. 1(C) shows the time-dependent percentage content changes of the fused liposomes (or liposome fusion efficiency), upon NIR irradiation. The uorescence of the Tb 3 -DPA complex increases and reaches a saturation value aer ca. one hour, and the calculated liposome fusion efficiency is ca. 30%. It should be noted that this experiment was performed in the presence of 1 mM EDTA in the extravesicular solution to ensure that the resulting uorescence does not originate from the light-induced lysis of the liposomes and the leakage of Tb 3+ and DPA, upon irradiation of the system (see the Experimental section, ESI †). In fact, we nd that the resulting uorescence, upon irradiation of the system, is very similar, in the presence or absence of EDTA, in the extravesicular solution, implying that the uorescence change was from the exchange of the components upon inter-fusion of the liposomes.
Control experiments conrm that no size changes or uorescence changes in the liposome mixture occur in the absence of NIR irradiation. These results demonstrate that the fusion of the liposomes and exchange of the loads are, indeed, induced by the NIR activation of the fusion process. The yield of the full fusion, leading to exchange of the liposome loads, is comparable to the yields reported for other liposome-liposome fusion processes. 62 In the next step, we examined the interactions of photoresponsive liposomes loaded with UCNPs and doxorubicin, DOX, an anti-cancer drug, with nucleic acid-functionalized cancer cells, e.g., HeLa cells, with the vision that the fusion between the liposome and the cell could lead to a cytotoxic effect on the cancer cells. Such dynamically triggered therapy against cancer cells would need, however, several issues to be resolved: (i) the fusion between the photoresponsive liposomes and the cells, and the subsequent release of the loads associated with the liposomes should be demonstrated. (ii) An element for the selective fusion of the liposomes with the cancer cells should be introduced to reach selective cytotoxicity towards cancer cells. In the rst steps described in Fig. S3 and S4, ESI, † several basic experiments conrming the fusion of the photoresponsive nucleic acid-functionalized liposome/HeLa mixtures were performed. In Fig. S3, † UV irradiation-triggered fusion of the liposomes L 3 with HeLa cells, functionalized with cholesterol-modied o-nitrobenzylphosphate caged hairpin nucleic acid (1) was examined. The liposomes L 3 were modied with nucleic acid (2) and FAM-functionalized nucleic acid (4) tethered at its 3 0 -end to cholesterol. The (1)-modied HeLa cells were irradiated with UV light (l ¼ 365 nm) to uncage (1) and induce the fusion between the liposomes and the cells. The confocal microscopy images conrmed the fusion between the liposomes L 3 and the HeLa cells, Fig. S3(B) † and accompanying discussion. In Fig. S4, † NIR irradiation-triggered fusion of the (1)-hairpin and the FAM-tethered nucleic acid (4)-functionalized liposomes L 4 , loaded with UCNPs, with HeLa cells modied with the cholesterol-functionalized nucleic acid (2) was performed. The NIR-irradiation of the L 4 /HeLa cell mixture leads to the UCNP-stimulated cleavage of the hairpins associated with L 4 . The resulting (1 0 /1 00 ) duplexes are displaced by the tethers (2) linked to the HeLa cells, and the contacted liposome/HeLa cell assembly results in the fusion of the liposomes with HeLa cells and the release of UCNPs into the cytoplasm. The confocal microscopy images, Fig. S4(B), † conrm the interconnection between the liposomes L 4 and the HeLa cells and the full fusion between the liposomes and the HeLa cells, resulting in the release of the luminescent UCNPs into the cells.
In the next step, we constructed a liposome/HeLa cell mixture, where the liposomes and HeLa cells were modied with appropriate nucleic acids, and the liposomes were loaded with UCNPs and doxorubicin (DOX), Fig. 2. The UCNP/DOXloaded liposomes were functionalized with the photoresponsive o-nitrobenzyl phosphate caged hairpin (1) modied at its 3 0 -end with cholesterol. The HeLa cells were modied with the 5 0 -end cholesterol-functionalized strand, (2). Irradiation of the liposome/HeLa cell mixture with NIR light, l ¼ 980 nm, resulted in the 365 nm-stimulated cleavage of the hairpins (1), and the hybridization of the fragmented strand (1 0 ) with the (2)-functionalized HeLa cells, leading to the fusion of the two compartments and to the incorporation of the UCNPs and DOX into the fused compartment, Fig. 2(A). The confocal uorescence microscopy images of the NIR-irradiated cells are presented in Fig. 2(B). Panel I shows the blue channel uorescence of the UCNPs incorporated into the HeLa cells, and panel II shows the red channel uorescence of the cell-incorporated DOX. Panel III presents the merged uorescence microscopy image of the cells. The microscopy images clearly indicate that the UCNPs and DOX are, indeed, released into the cell compartments as presented in Fig. 2(A). Fig. 2(C) shows the confocal microscopy images of the non-irradiated HeLa cell/ liposome system. No incorporation of the UCNPs and DOX into the non-irradiated cells is observed, implying that the lightinduced cleavage of the hairpin units associated with the liposomes is essential to allow the fusion of the liposomes with the cells, and the release of the UCNPs and DOX into the cells. Similar results are observed upon subjecting hESC normal cells to the UCNPs/DOX-loaded-(1)-modied liposomes, Fig. S5. † Thus, non-selective incorporation of the UCNPs and DOX into the HeLa and hESC cells occurs. Indeed, cytotoxicity tests, Fig. 2(D), reveal that the release of DOX into the cancer cells and the normal cells, results in comparable cytotoxicity towards the two types of cells. Entry II shows that no cytotoxic effect is observed in the non-irradiated mixture consisting of the UCNPfunctionalized DOX-loaded liposomes and the HeLa or the hESC cells aer two days of interaction. A signicant cell death (ca. 50%) is observed upon the NIR irradiation of the mixture consisting of the UCNPs-functionalized, DOX-loaded liposomes and the (2)-modied HeLa cells or the hESC cells. In these experiments, the L 1 liposome/HeLa cell mixture was irradiated with a NIR source for 10 minutes followed by the subsequent interaction of the mixture for two days, entry III. While effective cell death is observed, consistent with the NIR-stimulated fusion of the liposomes with the two cell membranes which results in the release of DOX into the cells, the process is not selective, and cytotoxicity toward the cancer cells and normal cells is observed.
To introduce cytotoxic selectivity towards the HeLa cells via the NIR-guided fusion of the UCNPs/DOX loaded liposomes with the cancer cells we apply specic aptamer-cancer cell receptor interactions as a means to guide the UCNPs/DOX to the cancer cells and specically release the DOX drug in the targeted cancer cell, Fig. 3(A). Since the MUC-1 receptor is overexpressed in the HeLa cell boundaries and since an anti-MUC-1 aptamer is available, we designed a strand (3) which includes the MUC-1 aptamer sequence conjugated to the tether "X" that is complementary to the fragmented strand generated upon the NIR-irradiation of the (1)-functionalized UCNPs/DOX-loaded photoresponsive modied liposomes. Challenging the HeLa cells with the strand (3) leads to the binding of (3) to the HeLa cells through aptamer-MUC-1 complex formation. The NIRirradiation of the mixture consisting of the (3)-functionalized HeLa cells and the UCNPs/DOX-loaded-(1)-functionalized liposomes leads to the light-induced cleavage of the photoresponsive o-nitrobenzyl phosphate caged hairpin (1). The fragmented tethers associated with the liposome boundaries hybridize with the domain X of strand (3), associated with the HeLa cells. This leads to the fusion of the liposomes with the cells and to the release of the UCNPs and DOX into the cells. Fig. 3(B), panels I-III show the confocal uorescence microscopy and merged images of the NIR-irradiated mixture composed of the UCNPs/DOX-loaded-(1)-hairpin-modied liposomes and the (3)-modied HeLa cells. The HeLa cells, panel I, reveal the blue uorescence of the UCNPs and the red uorescence, panel II, associated with DOX. The dual uorescence features of the uorescent constituents, panel III, indicate that the fusion of the liposomes with the HeLa cells occurred, resulting in the release of the UCNPs (blue uorescence) and DOX (red uorescence) into the cancer cells. For comparison, the hESC normal cells were pretreated with the MUC-1 aptameric strand (3). As these cells lack the MUC-1 binding sites, no binding (or low binding) of (3) to these cells occurs. The uorescence features of the NIR-irradiated mixture consisting of the UCNP/DOX-loaded-(1)-functionalized liposomes and the (3)-pretreated hESC normal cells are presented in Fig. 3(B), panels IV-VI. No blue uorescence of the UCNPs or red uorescence of DOX is detected in the cells indicating that no fusion of the liposomes occurred with the hESC cells. The merged image, panel VI shows, however, the elongated hESC cells that lack the UCNP/DOX loads. That is, the interaction of the cells with the MUC-1 aptamer-sequence (3) introduced selectivity for the incorporation of the UCNP/DOX-loaded-(1)functionalized liposomes into HeLa cancer cells. Further support for the selective light-induced incorporation of the UCNP/DOX-loaded-(1)-modied liposome is observed upon treatment of a mixture of HeLa cells and hESC normal cells with the liposomes and imaging the permeation of the UCNPs/DOX into the two types of cells, exhibiting different shapes. Fig. 3(C), panels I-III show the uorescence microscopy images and the merged image of the NIR-irradiated mixture of HeLa cells and hESC cells in the presence of the UCNP/DOX-loaded liposomes. The blue channel uorescence of the UCNPs and the red channel uorescence of DOX are observed in panels I and II, respectively, consistent with the release of the UCNPs/DOX upon fusion of the liposomes with the HeLa cells. The merged image, panel III, consists of the overlay of the uorescence images and the bright eld images of the mixture of cells. Clearly, the pink overlayed UCNP/DOX uorescence is visible on the structures of HeLa cells, yet no uorescence is observed on the hESC-elongated shaped cells (marked with dashed lines). These results are consistent with the selective fusion of the UCNP/DOX-loaded-(1)-modied liposomes with the HeLa cells. The selective fusion of the UCNP/DOX-loaded-(1)-modied liposomes, and the accompanying targeted release of the DOX drug into the HeLa cells suggest that the selective cytotoxicity towards the respective cells can be accomplished. Fig. 3(D) depicts the cytotoxicity experiments. In this study, in entry I, the hESC cells were treated with the MUC-1 aptamer and mixed with the UCNP/DOX-loaded-(1)-modied liposome, and the mixture was subjected to NIR irradiation. The viability of the cells aer two days corresponded to >95%. This result is consistent with the lack of fusion and release of DOX into the hESC cells. In entry II, the MUC-1 aptamer functionalized HeLa cells were interacted with the UCNP-loaded-(1)-modied liposomes and subjected to NIR irradiation. These liposomes lack DOX, yet still allow the light-induced fusion of the liposomes with the HeLa cells and the release of the UCNPs into the cells. Aer two days, the viability of the HeLa cells is over 95%. These results conrm that the UCNPs are non-toxic toward the HeLa cells. In entry III the mixture of the (3)-functionalized HeLa cells The results indicate that despite the fusion of the liposomes with HeLa cells proceeding, the viability of the cells is preserved, demonstrating that the UCNPs are non-toxic towards the HeLa cells. Entry III the HeLa cells treated with the UCNP/DOX-loaded liposomes L 1 and subjected to NIR-irradiation. The results demonstrate that the fusion of the liposomes and the HeLa cells, and the release of DOX lead to selective cytotoxicity towards the HeLa cells. and the UCNPs/DOX-loaded-(1)-modied liposomes was subjected to NIR irradiation to induce fusion and release of UCNPs and DOX into the HeLa cells. Aer two days of incubation, the viability of the HeLa cells decreased to 65%, implying that, indeed, the released drug killed specically the cancer cells. It should be noted that no cytotoxic effect on the hESC or HeLa cells was detected upon treating the cells with the UCNP/DOXloaded-(1)-functionalized liposomes, in the absence of primary NIR irradiation (see Fig. S6 and accompanying discussion in the ESI †). These results reconrm the need for NIR irradiation to induce the cleavage of the hairpin (1) associated with the liposomes. Only the cleaved fragment of (1) allows hybridization with the strand (3) associated with the HeLa cells and the subsequent fusion between the drug-loaded liposomes and the cancer cells. The selective fusion of the UCNPs/DOX-loaded-(1)-modied liposomes with the tether (3)-conjugated to cancer cell-specic aptamer complexes, and the selective release of DOX and cytotoxicity were further exemplied using MCF-7 breast cancer cells and MCF-10 normal epithelial breast cells (for a detailed presentation of the results see Fig. S7-S10, † and accompanying discussion). Thus, the approach presented by us provides a versatile tool for targeting the therapeutic effects of drugs towards cancer cells. It should be noted that the distribution of the uorescent DOX in the HeLa cells could proceed by two alternative pathways: (i) fusion of the liposomes with the cell-membrane followed by release of DOX. (ii) Endocytosis of the liposome into cells followed by intracellular degradation of the liposomes which leads to the release of the drug. We nd, however, the distribution of DOX in the cells proceeds on a time-scale of 25 to 30 minutes. This time-scale is very similar to the exchange rate of the contents of the fused liposomes (cf. Fig. 1(C)). Since the endocytosis of liposomes into cells is anticipated to be much slower (time scale of hours), the fusion pathway to release DOX is supported.

Conclusions
The present study has introduced upconversion nanoparticle (UCNP)-loaded liposomes functionalized with photolabeled onitrobenzyl phosphate caged hairpin nucleic acid structures as functional carriers that induce photostimulated liposomeliposome fusion and liposome-cell membrane fusion processes. The UCNPs allow the NIR-irradiation of the hairpin-modied liposomes (l ¼ 980 nm) and the generation of localized UV light (l ¼ 365 nm) that deprotects and separates the hairpin structure. In the presence of nucleic acid-modied liposomes, complementary to the uncaged, hairpin-fragmented modied liposomes, inter-liposome, duplex-crosslinked structures are formed leading to the spatiotemporal fusion of the liposomes. The labeling of the separated liposomes with Tb 3+ and 2,6-pyridinedicarboxylic acid, DPA, leads to the exchange of loads and the formation of the Tb 3+ -DPA uorescent complex that allows the quantitative evaluation of the inter-liposome fusion efficiency (ca. 30%). The successful NIR photostimulated spatiotemporal fusion of liposomes by complementary nucleic acid bridges paves the way to spatio-temporal fusion of liposomes by other stimuli-responsive, recongurable nucleic acid crosslinkers. For example, by the modication of the two kinds of liposomes with aptamer subunits interconnection of liposomes and their fusion, through the formation of the respective ligand-aptamer complex, may be envisaged. Alternatively, the functionalization of the two kinds of liposomes with T-rich tethers and A rich tethers, respectively, is anticipated to interlink and fuse the liposomes through their crosslinking by T-A$T bridges. In addition, our study demonstrated the selective UCNP-photostimulated fusion of drug (doxorubicin)-loaded liposomes with HeLa cancer cells and the selective cytotoxicity of the drug-loaded liposomes towards the HeLa cancer cells, as compared to normal hESC cells. In this system, UCNPs/doxorubicin were loaded in the liposomes functionalized with the onitrobenzyl phosphate photo-labeled, caged, hairpin structures. The HeLa cancer cell membranes were functionalized with a nucleic acid that included the MUC-1 aptamer sequence conjugated to a nucleic strand complementary to the uncaged, fragmented, hairpin units associated with the liposomes. The aptamer units bind to the MUC-1 receptor sites associated with the HeLa cells, introducing surface functionalities for liposome-cell membrane fusion. The UCNP photostimulatedcleavage and fragmentation of the hairpin units modifying the liposomes allowed, then, the inter-hybridization of the complementary nucleic acids modifying the liposomes and cell membrane, leading to the fusion of the components, and to the release of the drug into the HeLa cells. The selective cytotoxicity of the doxorubicin-loaded liposomes towards HeLa cells is due to the aptamer guided interconnection between the liposomecancer cell entities. The system paves the way to use liposomes loaded with other anti-cancer drugs as selective carriers for therapeutic treatment of cancer cells via the liposome-cancer cell fusion process. In addition, by using aptamer conjugates specic to other cancer cell biomarkers, and the appropriate engineering of the photo-responsive hairpin structures associated with the liposomes, versatile, selective targeted cytotoxicity towards different cancer cells may be envisaged.

Conflicts of interest
The authors declare no competing nancial interest.