Imported: 10 Mar '17 | Published: 27 Nov '08
USPTO - Utility Patents
The invention concerns the field of molecular probe architecture for in vivo imaging. More particularly, the invention concerns molecular constructs providing an imaging function activable in intracellular environment, said constructs being further bound to a vector which enables certain cells to be targeted, and said cells to be internalized. The inventive fluorescence probes enable in particular images of certain targeted tissues to be formed, while maintaining a low background noise level and, preferably, while obtaining at the targeted tissue, an imaging signal increasing in time.
The present invention relates to the field of the architecture of molecular probes for in vivo imaging. More particularly, the invention relates to molecular constructs providing a fluorescence imaging function activatable in an intracellular medium, these constructs also being bound to a vector which allows the targeting thereof to certain cells, and internalization in the cells in question.
The recent development of optical methods for fluorescence imaging in vivo in small animals opens up new horizons for functional imaging. It is now possible to follow, in real time and noninvasively, what becomes of luminescent molecules, and their biodistribution, and to establish a diagnosis and evaluate the effect of a therapy by virtue of these molecules. The advantages of optical imaging compared with the other functional imaging techniques (MRI, PET, SPECT) are the following:
Currently, functional optical imaging is essentially carried out using luminescent labels grafted to a biological ligand which makes it possible to target certain regions of the individual (organs, cells, tumors, etc.).
Various luminescent labels have been developed for this type of imaging. Firstly, mention may be made of probes based on organic fluorophores. The first label used, ICG (Indo Cyanin Green), was, very early on, used naked (injection of the fluorophore alone), for imaging/visualizing vascularization and circulation in the blood vessels; these organic fluorophores have subsequently been grafted onto proteins or antibodies for targeting various cells (Folli, Westerman et al. 1994; Neri, Carnemolla et al. 1997; Ballou, Fisher et al. 1995; Ballou, Fisher et al. 1998; Becker, Riefke et al. 2000). However, coupling to these large molecules has drawbacks with respect to targeting and pharmacokinetics (Bugaj, Achilefu et al. 2001); consequently, the functionalization of fluorophores with small peptides has recently been preferred (Achilefu, Dorshow et al. 2000; Bugaj, Achilefu et al. 2001; Licha, Hessenius et al. 2001; Becker, Hessenius et al. 2001).
A second type of label for in vivo fluorescence imaging is the class of probes based on luminescent semiconductor nanocrystals (Michalet, Pinaud et al. 2005). The major drawback of these labels is their poor pharmacokinetics, which necessitate a special chemical coating (Ballou, Lagerholm et al. 2004; Gao, Cui et al. 2004). A single publication has up until now been published regarding such functionalized luminescent labels for targeting tumors (Gao, Cui et al. 2004).
However, the labels presented above exhibit a major limitation related to the nonspecific signal originating from the nontargeted parts of the individual's body. In fact, the existing biological ligands do not allow 100% targeting, and the targeting kinetics may be slow. Furthermore, during this period of time in which the probe binds to its receptor, said probe is already beginning to be metabolized by the organism. Under these conditions, the optimal time period for observation of the targeted biological process, i.e. the time period during which the region of interest/rest of the animal's body contrast is greatest, may be short and difficult to determine. In addition, the region of interest/rest of the individual's body contrast that is obtained remains low. This problem is even more essential for fluorescence imaging than for the other imaging techniques, since the very high degree of light scattering in the tissues means that the level of the nonspecific signal is very high. This thus makes any tomographical method for locating the probes difficult to implement.
In order to improve the targeting, certain teams have proposed, rather than simply grafting the luminescent label to a biological ligand for targeting the region to be imaged, using more complex vectors. Thus, the use of nanoparticles, such as polymer nanoparticles (Weissleder, Tung et al. 1999; Bremer, Tung et al. 2001) or semiconductor nanocrystals (therefore playing both the role of vector and the role of luminescent label (Michalet, Pinaud et al. 2005)), is beginning to be widespread. Nevertheless, the grafting of various entities onto these nanoparticles is complex; thus, only the functionalization of luminescent semiconductor nanocrystals with a targeting entity (Gao, Cui et al. 2004) and the functionalization of polymer particles with an imaging function (Weissleder, Tung et al. 1999; Bremer, Tung et al. 2001) have been proposed.
Recently, two molecular assemblies, capable of constituting alternatives to nanoparticles for carrying targeting functions and a label for fluorescence imaging, have been described (Boturyn, Coll et al. 2004; Dumy, Favrot et al. 2004; Maison, Frangioni et al. 2004). The first, called RAFT (Regioselectively Addressable Functionalized Template), is a cyclodecapeptide; the second is an adamantane derivative.
Another approach for reducing the background noise during the use of fluorescent probes consists in using probes that are specifically activatable in certain cells.
The principle of the first-generation activatable probes is to use a PEG/polylysine polymer as vector (Weissleder, Tung et al. 1999). A Cy5.5 fluorophore is bound to the polymer backbone via a pendent arm. The ratio of the number of fluorophores per unit of polymer is optimized such that the Cy5.5s are sufficiently close for their fluorescence to be self-quenched, and for the probe to be initially very weakly fluorescent. Certain enzymes, in particular overexpressed in certain tumor models, are capable of cleaving the polymer backbone. Under the action of these enzymes, the fluorophores are therefore separated and capable of emitting. For example, Weissleder et al. measure, with this probe, a fluorescence signal 80 times higher in a tumor model than in the blood, although the concentration of probes therein is 10 times lower (Weissleder, Tung et al. 1999).
The second generation of activatable probes adapts the principle for specific imaging of a proteolytic enzymatic activity (i.e. capable of cleaving a protein) (Bremer, Tung et al. 2001). This time, the pendent arm between the polymeric backbone and the fluorophore is a peptide arm, specific for the enzymatic activity to be imaged. Thus, the peptide used will vary according to whether it is desired to image MMP2 activity (Bremer, Tung et al. 2001), cathepsin D activity (Tung, Bredow et al. 1999; Tung, Mahmood et al. 2000) or thrombin activation in the blood (Tung, Gerszten et al. 2002).
More recently, this group has used the principle, no longer of self-quenching of the fluorescence of the same fluorophore, but of quenching of the fluorescence of a fluorophore by another quencher (Pham, Choi et al. 2005). These photophysical and photochemical processes are well known to those skilled in the art and are described, for example, in the work by J. Lakowicz (Lakowicz 1999). They are used for imaging an enzymatic activity: after enzymatic cleavage of the peptide arm, the fluorophore and its quencher are separated and the fluorophore can then emit (Pham, Choi et al. 2005).
The probes proposed in these studies are therefore probes which are initially nonfluorescent, and the fluorescence of which is triggered only in the areas where there exists the enzymatic activity to be imaged and for just such a purpose the probes were structured. However, these probes have the following drawbacks:
There exists, therefore, at this time a real need for a targeted imaging vector which is such that the background noise in the nontargeted regions is zero or virtually zero, and that the intensity of the emission signal, in the targeting region, is independent of a specific enzymatic activity (present only in certain cell types, or of varying level depending on the cells), in order to obtain an image that faithfully reflects the targeting itself. The aim of the present invention is to provide imaging tools that remedy at least some of the drawbacks of the current vectors, as disclosed above.
For this, the inventors have developed a molecular system which allows the activation of an imaging function in the intracellular medium of any eukaryotic cell. The coupling of such a system to a targeted vector which is internalized in the target cells enables the emission signal to be triggered only after a target cell has been attained.
A first subject of the invention is therefore a targeted biological vector having an imaging function activatable in the intracellular medium, and such that the imaging function is activated by an ubiquitous mechanism. The term ubiquitous mechanism is herein intended to mean a mechanism which occurs in the intracellular medium of any eukaryotic cell. In the following text, an imaging function will denote the function itself, but also, by misuse of language, the means (fluorophores, luminescent particles, etc.) for obtaining this function. Similarly, a targeting function can denote the means used for the targeting (ligands, antibodies, etc.). A targeted biological vector comprising an imaging function may also be called a probe.
According to a preferred embodiment of the vector of the invention, the activatable imaging function is provided by a fluorophore F linked to a fluorescence quencher by an arm cleavable in the intracellular medium. The internalization of the vector, subsequent to its binding to the target cell, will bring about the cleavage of the arm linking the fluorescence quencher to the fluorophore, and therefore the activation of the fluorescence. FIG. 1 illustrates this embodiment of the invention. The probe according to the invention is represented therein by the formula vector-R1-XYR2, where vector denotes the targeted vector, R1 and R2 are groups each containing a fluorophore or a fluorescence quencher, and XY represents the bond cleavable in an intracellular medium. A group Z, symbolizing a drug (therapeutic molecule, for example) is, where appropriate, attached to Y and/or to R2. In addition, the groups R1 and R2 may comprise a chemical bonding group for the attachment of said fluorophore or fluorescence quencher to the vector or to the arm that is cleaved (or, optionally, to the drug Z), and, where appropriate, a chemical spacer which makes it possible to reduce the steric interactions between, firstly, the vector and/or the arm that is cleaved and, secondly, the fluorophore and/or the fluorescence quencher. In the remainder of the present text, the notations R1, R2, X, Y and Z keep this meaning.
By way of examples of fluorophores F that can be used, mention may be made of:
These fluorophores may be bonded to the vector and/or to the cleavable arm in particular by amide, ester, thioether or thioester functions. As mentioned above, a spacer arm between the vector and/or the cleavable arm and the fluorophore may also be present, in particular for reducing any possible quenching of the fluorescence of the fluorophore by the vector and/or the cleavable arm.
By way of nonfluorescent fluorescence quenchers, mention may be made of:
These fluorescence quenchers may be bonded to the vector and/or to the cleavable arm by amide, ester, thioether or thioester functions, or the like. A spacer arm between the vector and/or the cleavable arm and the fluorescence quencher may also be present.
Some nonlimiting examples of structures of fluorophores and of fluorescence quenchers are given in FIG. 3.
The arm linking the fluorescence quencher and the fluorophore is preferably cleavable in the intracellular medium of any cell. The cleavage of the XY bond may, for example, be an acid-based, redox or organometallic reaction, possibly catalyzed by an enzyme. According to a preferred embodiment of the invention, the arm cleavable in an intracellular medium comprises a disulfide bridge. An example of an arm that can be used comprises a disulfide bridge between two cysteines (XY=Cys, the bond between the two cysteines being an SS bond and not a peptide bond, the XY bond then being referred to as Cys-SS-Cys). Another example is an arm which simply consists of two sulfur atoms (XYS). When the cleavable arm comprises a disulfide bridge, the cleavage is catalyzed enzymatically by thioredoxins, in the lysosomes and endosomes of the cells (Arunachalam, Phan et al. 2000). Thioredoxins are small proteins involved in intracellular redox regulation, and therefore in numerous fundamental processes (response to stress, apoptosis, etc.). They reduce all the disulfide bridges of proteins entering the cell, but, unlike proteases, do not destroy the peptide bond between amino acids. They are present in all cells of all organisms.
In the context of the present invention, a large variety of structures may be used to constitute the core of the vector. The term core of the vector is herein intended to mean the molecule or the particle to which the imaging and targeting functions are bound. By way of examples of structures that can be used for the core of the vector, mention may be made of:
According to a preferred embodiment of the vectors according to the invention, the targeting is provided by at least one biological ligand recognized by a receptor overexpressed at the surface of certain cells. The biological ligands for specifically targeting certain cells may be:
Their targeting activity is due to the molecular recognition of these ligands by receptors overexpressed at the surface of the cells of the region of interest.
Ligands that are particularly preferred for implementing the invention are, for example, peptides comprising the RGD motif, such as cyclo(RGDfK), cyclo(RGDyK) or cyclo(RGDfV). These peptides recognize the v3 integrin which is overexpressed at the surface of tumor cells and of endothelial cells during tumor neoangiogenesis. The use of these ligands in the vectors according to the invention therefore makes it possible to image the tumors and their vascularization, and, where appropriate, to deliver a drug to this site. Another preferred ligand is, for example, a peptide comprising the NGR motif described by Curnis et al. (Curnis, Arrigoni et al. 2002), which also targets neovessels.
According to a specific embodiment of the invention, the vector may comprise one or more label(s) for an imaging method other than fluorescence imaging, either in addition to the latter or as a replacement for the latter. These labels may be grafted to the surface of the vector, or encapsulated inside if this is a vector of nanoparticulate type; alternatively, the core of the vector may itself be a contrast agent (for example, an iron oxide nanoparticle, as contrast agent for MRI). Such labels may be:
According to a specific embodiment of the invention, the vector is also capable of delivering a drug Z. This drug may be attached to the vector or to the cleavable arm by various chemical groups (for example: acid, ester, thioether or thioester functions) optionally via a spacer arm. It may also be bound to the vector by a cleavable arm, such as the arms of XY described above, or by another arm that is chemically cleavable or cleavable by another process (activation by light, ultrasound, radiofrequency, etc.). It may also be encapsulated in the vector. When the drug is either linked to the vector by the same cleavable arm as that contained in the imaging function, or is itself labeled with the fluorophore or the quencher of fluorescence of the imaging function, the activation of the imaging function also indicates the delivery of the drug.
The term drug is herein intended to mean any molecule capable of having an effect on the cell into which it will be delivered. This effect is preferably therapeutic for the individual to whom it is administered. By way of examples of drugs Z that can be used in the context of the invention, mention may be made of:
According to a specific embodiment of the invention, the activatable imaging function is provided by a fluorophore F linked to a fluorescence quencher by an arm cleavable in the intracellular medium, such that, after cleavage of said cleavable arm, the quencher remains bound to the vector and the fluorophore remains bound to the drug Z. According to the notation used in FIG. 1 and explained above, this implies that the drug Z is bound to the group R2 and/or to Y.
Several configurations of this embodiment, or of the embodiment vector-R1-XYR2 in the absence of drug Z, can be envisioned and readily implemented by those skilled in the art, depending on the application chosen. These various configurations are illustrated in FIG. 1C, and are an integral part of the invention.
In the case illustrated in FIG. 1C.1, the fluorophore F is on the group R1, and R2 comprises a nonfluorescent quencher of the fluorescence of F (R2 may be limited to this quencher). After activation of the imaging function, fluorescent labeling of the vector is then obtained, which makes it possible to visualize the targeting of the probe and to follow the biodistribution of the vector itself.
FIG. 1C.2 illustrates the case where the fluorophore F is on the group R2, and where a nonfluorescent quencher of the fluorescence F is on R1. After activation of the imaging function, fluorescent labeling of the cleaved product R2-Y or R2-Y-Z or Y-R2-Z is then obtained, which makes it possible to visualize the targeting of the probe and to follow the biodistribution of the cleaved product and therefore, where appropriate, of the drug Z delivered.
In the case where the same fluorophore F is on the group R1 and on the group R2, F should be a fluorophore whose fluorescence is capable of self-quenching. This is the case, for example, of the fluorophores of the cyanin family. The activation of the imaging function then makes it possible to visualize the targeting of the probe and to follow the vector and the cleaved product, without distinction. The fluorescence released is in this case potentially twice that released in the cases disclosed above and illustrated in FIGS. 1C.1 and 1C.2.
It is also possible to use a second fluorophore as fluorescence quencher. In this case, the two fluorophores F1 and F2 (with F1F2) are chosen such that the fluorophore F1, excited at its excitation wavelength exc (1), initially has its fluorescence quenched by the fluorophore F2 via the energy transfer process well known to those skilled in the art (Lakowicz 1999). There is then, initially, only an emission signal at the emission wavelength of F2, em (2), and not at the emission wavelength of F1, em (1) (FIG. 2). The activation of the imaging activity is reflected by the emission of a signal at the emission wavelength of F1, em (1) during excitation at exc (1).
In the case, illustrated in FIG. 1C.3, where the fluorophore F1 is on the group R1 and the fluorophore F2 is on the group R2, this signal indicates the targeting of the probe and makes it possible to visualize the biodistribution of the vector by exciting the system at the excitation wavelength of F1, exc (1), and detecting the signal at the emission wavelength of F1, em (1), and to visualize the biodistribution of the cleaved product by exciting the system at the excitation wavelength of F2, exc (2), and detecting the signal at the emission wavelength of F2, em (2) (FIG. 2). Excitation at the emission wavelength of F1, exc (1), and detection at em (2), also makes it possible to follow the biodistribution of the probe before activation of the imaging function (FIG. 2). Such a configuration therefore has the advantage of following both the biodistribution of the probe (by exciting at exc (2) and observing at em (2)), and the activation of the imaging function (by exciting at exc (1) and observing at em (1)) (FIG. 2). It is therefore one of the most advantageous configurations of the invention.
The roles of F1 and F2 may be reversed, i.e. F1 and F2 may be chosen such that the fluorophore F2, excited at its excitation wavelength exc (2), initially has its fluorescence quenched by the fluorophore F1. The activation of the imaging function will bring about the same result, i.e. visualizing the targeting of the probe and visualizing the biodistribution of the vector by exciting the system at the excitation wavelength of F1, exc (1), and detecting the signal at the emission wavelength of F1, em (1), and visualizing the biodistribution of the cleaved product by exciting the system at the excitation wavelength of F2, exc (2), and detecting the signal at the emission wavelength of F2, em (2).
The invention therefore also relates to the use of a vector as described above (configuration with two fluorophores F1 and F2), for delivering a drug, for example a therapeutic molecule, and simultaneously following the biodistribution of the vector and of the drug in question. This configuration, and also that in which R2 comprises a fluorophore F and R1 a pure fluorescence quencher, may also be used advantageously to follow, in real time, the biodistribution of a drug. The term pure quencher is herein intended to mean a fluorescence quencher which is itself nonfluorescent.
Preferably, a vector according to the present invention is electrically neutral before activation of the imaging function. This is because a neutral molecule penetrates more easily into the cell than a charged molecule. Thus, in the examples which follow, the vector RAFT-Cy5-Cys-SS-Cys-Q penetrates into the cells better than the vector RAFT-Cy5-Cys-SS-Cys-Cy5. It is, moreover, advantageous for the two molecules derived from the cleavage of the arm XY to be charged, since charged molecules remain more readily in the intracellular medium. Thus, in the example described later, the cleavage of the disulfide bridge of the vector RAFT-Cy5-Cys-SS-Cys-Q (RAFT also being bound to a neutral ligand providing the targeting, and it being possible for the quencher Q to be coupled to an electrically neutral drug) gives two molecular entities of opposite charges.
According to a preferred embodiment of the vectors of the invention, the imaging function is therefore provided by a cyanin, for example the Cy5 fluorophore, linked by a disulfide bridge to a quencher of its fluorescence.
The results given in the experimental section below show that a vector according to the invention has pharmacokinetic properties such that the imaging response, in the region targeted, increases over time (FIG. 12), at least during the first hour following injection of the vector. This is at least in part related to the fact that the activation of the fluorescence takes place in the intracellular medium, and therefore only after the vector has reached a target cell and has been internalized. The use of a disulfide bridge, such that cleavage of the SS bond results in activation of the imaging function, allows good signal appearance kinetics. FIGS. 5, 6, 10 and 11 show that the kinetics of chemical cleavage of the disulfide bridge by 2-mercaptoethanol (2-MCE) is slow, despite the high concentration of 2-MCE. The cleavage is even slower in the cell, since the concentration of enzyme is low. This results in a slow increase in the intensity of the signal, which remains for a long time and allows elimination of the nontargeted probe during this time, which favors specificity. This property of the vectors of the invention is particularly advantageous, since it gives the practitioner greater freedom of maneuver for acquiring the imagespecific for the targeted regionunder good conditions. This property of the vectors described herein is therefore an important aspect of the invention.
The examples and figures given below in a nonlimiting manner will make it possible to demonstrate certain advantages and characteristics, and also other advantageous arrangements, of the present invention.
The embodiment of the invention described below is based on the use:
The chemical structure of this molecule is given in FIG. 4. It was prepared from cysteine (0.4 mg, 1.6 mol) and from the activated N-hydroxysuccinimide ester of cyanin 5 (2.8 mg, 3.5 mol) in a solution of DMF/H2O (6:1) at pH 8.0. The product is obtained after purification by HPLC, in the form of a blue powder (1.2 mg, 0.8 mol, 50%). FIG. 5 shows that the fluorescence of the Cy5 fluorophores is indeed initially self-quenched, and is completely released by chemical cleavage of the SS disulfide bridge.
The chemical structure of this molecule is given in FIG. 4. It was prepared from Boc-cysteine(Npys) (210 mg, 0.56 mmol). The Boc group is first of all eliminated in a solution of TFA/DCM (1:1) (138 mg, 0.5 mmol, 90%). Then, cyanin 5 N-hydroxysuccinimide (5 mg, 6.3 mol) in a solution of DMF/H2O (9:1), at pH 8.0 is added to a solution of cysteine(Npys) (1.7 mg, 6.3 mol). After purification of the compound, cysteineOMe (6.1 mg, 6.1 mol) is added and the pH is adjusted to 7.0 in water. Purification by HPLC gives the compound Cy5-Cys-SS-CysOMe in the form of a blue powder (2.4 mg, 2.5 mol, 52%). This compound (2.4 mg, 2.5 mol) is then taken up with QSY21 succinimide ester (2 mg, 2.5 mol) in DMF at pH 8.0. Purification by HPLC gives the desired product in the form of a blue powder (2.2 mg, 1.3 mol, 54%). FIG. 6 shows that the fluorescence of the Cy5 fluorophore is indeed initially quenched by the QSY21, and is completely released by chemical cleavage of the SS disulfide bridge.
FIG. 7 shows that the fluorescence of the imaging functions is not released when they are circulating in the blood in mice. It also shows that no nonspecific adsorption of the Cy5-Cys-SS-Cys-QSY21 imaging function occurs on the blood proteins, whereas 25% adsorption occurs for the Cy5-Cys-SS-Cys-Cy5 function.
FIG. 8 confirms these results: after intravenous injection of the imaging functions, no fluorescence is observed, unlike the case of the nonfunctionalized Cy5 fluorophore.
FIG. 9 gives the structure of the cysteine(Cy5)-SS-cysteine(Cy5)RAFTc[RGDfK-]4 molecule. The cysteine(Npys)RAFTc[-RGDfK]4 peptide (10 mg, 2.26 mol) is taken up in 0.5 ml of DMF/PBS, pH 4.8, 3/1 with cysteine (0.3 mg, 2.7 mol). The product is purified by HPLC (5.3 mg, 53%). The cysteine-SS-cysteineRAFTc[-RGDfK]4 peptide (3.5 mg, 0.79 mol) is taken up in 300 l of DMF with cyanin 5 N-hydroxysuccinimide (1.9 mg, 2.4 mol). The final product is purified by HPLC and obtained in the form of a blue powder (2.4 mg, 54%).
FIG. 10 shows that the fluorescence of the Cy5 fluorophores is indeed initially self-quenched, and is completely released by chemical cleavage of the SS disulfide bridge.
FIG. 9 gives the structure of the cysteine(Cy5)-SS-cysteine(QSY21)RAFTc[RGDfK-]4 molecule. The cysteine-SS-BoccyssteineRAFTc[RGDfK-]4 peptide (19.9 mg, 4.45 mol) is taken up in 0.4 ml of DMF with cyanin 5 N-hydroxysuccinimide (3.1 mg, 3.91 mol). The solvent is removed under reduced pressure and the cysteine(Cy5)-SS-BoccysteineRAFTc[RGDfK-]4 peptide is taken up in 6 ml of 95/2.5/2.5 TFA/TIS/H2O and purified by HPLC, and obtained in the form of a blue powder (11.5 mg, 51%). The cysteine(Cy5)-SS-cysteineRAFTc[RGDfK-]4 peptide is taken up in 300 L of DMF with QSY21 N-hydroxysuccinimide (1.13 mg, 1.39 mol) and purified by HPLC, and obtained in the form of a blue powder (1.2 mg, 20%).
FIG. 11 shows that the fluorescence of the Cy5 fluorophore is clearly initially self-quenched, and is completely released by chemical cleavage of the SS disulfide bridge.
The molecular vectors RAFT-(cRGD)4-Cy5-Cys-SS-Cys-Cy5 and RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21 can be used for specifically imaging the endothelial cells of tumors overexpressing v3 integrin receptors, such as IGROV-1 cells (human ovarian cancer model) implanted subcutaneously into a nude mouse.
The optical imaging is carried out by means of a commercially available or prototype fluorescence imaging device. The probes injected intravenously remain nonfluorescent in the animal's body outside the tumor (FIG. 8). After specific targeting of the tumors by the RGD ligand, the probes are internalized into the tumor cells. In the intracellular medium, the imaging functions are activated (FIG. 12). The subject of the invention therefore allows noninvasive optical imaging of tumors by means of a fluorescence imaging device, in vivo. It consequently makes it possible to follow the evolution of tumors over time or in response to a therapeutic treatment.
The mice used are female nude mice 6 to 8 weeks old, maintained under pathogen-free conditions. The IGROV-1 cells (human ovarian cancer model) are cultured in an RPMI 1640 culture medium containing 1% of glutamine, 10% of FCS, 50 U/ml of penicillin and 50 g/ml of streptomycin. The cells are maintained at 37 C. under a humid atmosphere with 5% of CO2. 10106 cells are injected subcutaneously into the back of the mice 2 weeks before injection of the molecular vectors RAFT-(cRGD)4-Cy5-Cys-SS-Cys-Cy5 and RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21. The latter are injected into the tail intravenously, in 100 l of PBS (pH 7.1, 9.5 mM), at doses of 10 nmol/mouse.
The anesthetized mice are imaged with a fluorescence reflectance imaging (FRI) device, comprising as excitation source a crown of LEDs equipped with interference filters, emitting at 633 nm (illumination power 50 Wcm2). The images are collected after filtration with an RG665 colored filter of optical density 5 at the excitation wavelength by means of a CCD camera (Orca BTL, Hamamatsu), with an exposure time of 100 ms. The signals are quantified using image processing software.
The results obtained are represented in FIG. 12. It appears that the activatable probes RAFT-(cRGD)4-Cy5-Cys-SS-Cys-Cy5 and RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21 produce more signal in the tumor than in the probe RAFT-(CRGD)4-Cy5-Cys-SS-cysteine, and bring about a gradual appearance of the signal in the tumor, as the probe is activated (and then its disappearance through elimination), whereas the probe RAFT-(cRGD)4-Cy5-Cys-SS-cysteine produces a signal which decreases very rapidly over time (FIG. 12A). Consequently, the contrast, i.e. the ratio of signal obtained between the tumor and the skin, increases when going from the probe RAFT-(cRGD)4-Cy5-Cys-SS-cysteine to the probes RAFT-(cRGD)4-Cy5-Cys-SS-Cys-Cy5 and RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21 (FIG. 12B).
The imaging functions described herein therefore clearly make it possible to obtain, due to the fact that the fluorescence of the probe is activated gradually and in a targeted manner in the tumors, a background noise that is lower in the rest of the animal's body than the corresponding targeted conventional probe.
The penetration into the cells of the probes RAFT-(cRGD)4-Cy5, RAFT-(cRGD)4-Cy5-Cys-SS-Cys-Cy5 and RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21 was observed on Hek3 cells, after 1 to 2 hours of incubation. The results, given in FIG. 13, show that, with the RAFT-(cRGD)4-Cy5 probe, the fluorescence remains at the periphery of the cells (column 2); the cells incubated with RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21 show a clear fluorescence inside the cells (column 4), whereas, with the RAFT-(cRGD)4-Cy5-Cys-SS-Cys-Cy5 probe (column 3), a large amount of fluorescence is still visible at the level of the cell membrane, which proves that the probe does not enter well. These results illustrate the fact that a neutral molecule (in the case in point, RAFT-(cRGD)4-Cy5-Cys-SS-Cys-QSY21) penetrates into the cells better than a charged molecule.
The toxicity of the imaging functions Cy5-Cys-SS-Cys-Cy5 and Cy5-Cys-SS-Cys-Q was compared. 10 ml of solution of Cy5-Cys-SS-Cys-Cy5 or of Cy5-Cys-SS-Cys-Q (not grafted onto a vector), at approximately 0.5 M in PBS, were incubated in the presence of TSA cells (approximately 20106 cells/flask). Samples were taken from the solution at various time periods.
The results are given in FIG. 14. It is observed that, in the case of Cy5-Cys-SS-Cys-Cy5, the solution becomes cloudy, which is reflected by considerable scattering by the solution, and therefore an increase in absorbance, in particular at 800 nm, a wavelength for which the Cy5, Cy5-Cys-SS-Cys-Q and Cy5-Cys-SS-Cys-Cy5 molecules do not normally absorb. This cloudiness of the solution, which means that it scatters light, is interpreted as being due to the fact that the cells have detached from the walls of the culture flask, indicating that they have been destroyed by Cy5-Cys-SS-Cys-Cy5. In the case of the incubation in the presence of Cy5-Cys-SS-Cys-Q, the cell death (and therefore the cell detachment) begins to exist only after 1 h of incubation and is to a much lesser degree. The Cy5-Cys-SS-Cys-Cy5 molecule at 0.5 M therefore causes cell death in the TSA cells, from the first minutes of incubation onward, unlike the Cy5-Cys-SS-Cys-Q molecule.