Local Drug Delivery by Fibrin Glue for Glioma Treatment: Enhancing Drug Efficacy by Photochemical Internalization (PCI)

Abstract

Background

Localized methods of drug delivery, such as controlled drug release from fibrin glue (FG), has the potential of improving the efficacy of chemotherapy for brain tumors by bypassing the blood brain barrier. Photochemical internalization (PCI) of bleomycin (BLM) and doxorubicin (DOX) has been shown to enhance the cytosolic delivery of drugs in localized site and temporal specific manner. This study examined the ability of PCI to enhance the growth inhibiting effects of BLM or DOX released from FG on multi-cell glioma spheroids in vitro.

Materials and methods

FG layers consisted of a 1:1 ratio of fibrinogen and drug or photosensitizer loaded thrombin. Supernatants covering the FG layers were harvested from the gelled FG containing wells after 2, 24, 48 and 72 hours. F98 glioma cells in suspension were incubated with the photosensitizer aluminum phthalocyanine disulfonate (AlPcS_2a, 1 μg/mL) for 2 hours, washed and formed as 3D spheroids. The spheroids were incubated with BLM or DOX released from FG. One hour later, the spheroids were treated with light (PCI), λ = 670 nm, from a diode laser at an irradiance of 2.0 mW/cm². Spheroid growth was monitored for an additional 14 days.

Results

At the BLM or DOX concentrations used in these experiments to load the FG, spheroid growth was not significantly influenced by the BLM or DOX that was released from the FG gels. In contrast, spheroid growth was significantly inhibited or completely suppressed by PCI of released drug from either FG-BLM or FG-DOX.

Conclusion

The results of the present study show that drug was released in a non-degraded form for an extended time period. The growth inhibition caused by either FG released BLM or DOX was significantly enhanced by AlPcS_2a mediated PCI.

Keywords

Photochemical Internalization, PCI, Fibrin Glue, Bleomycin, Doxorubicin

Introduction

The Central Brain Tumor Registry shows that gliomas account for 34% of all primary brain tumors, and 82% of all malignant primary brain tumor cases. Despite continued efforts, glioblastoma multiforme (GBM) remains an incurable form of primary brain cancer. Even in cases of gross tumor resection (as determined from post-operative MRI), the tumor invariably recurs. In approximately 80% of all cases, recurrent tumor growth occurs within a 2-3 cm margin of the surgical resection cavity [1,2]. This is likely due to the migratory behavior of glioma cells - a trait attributed to their developmental character within the CNS. Both individual cells and micro-colonies of tumor cells have been shown to infiltrate in or beyond a region of brain-adjacent-to-tumor (BAT) - a zone that may extend several cm from the resection margin. Eradication of these infiltrating glioma cells poses a significant clinical challenge due to the fact that migratory tumor cells in and beyond the BAT are protected to varying degrees by the blood brain barrier (BBB). This formidable protective barrier unfortunately also severely limits the efficacy of systemically delivered chemotherapeutic and or nano-agents that cannot pass through the BBB.

One method of bypassing the BBB is the local application of chemotherapeutic drugs directly into the resection cavity during the surgical procedure. Localized drug delivery permits increasing the drug dose able to reach the remaining infiltrative tumor cells in the brain parenchyma while avoiding systemic side effects. For this type of local drug application to function adequately the drug should be delivered in a sustained release form. Several types of slow release vehicles have been evaluated for GBM treatment such as clinically approved BCNU biodegradable wafers [3] as well as various forms of hydrogels in experimental animals [4]. One form of hydrogel, fibrin glue (FG), has several characteristics that make it well suited for this form of drug delivery. In particular, it has been used clinically in surgery both as a sealant and to obtain hemostasis for decades, so its lack of toxicity has been clearly proven. FG loaded with drugs therefore has been researched as a localized controlled release vehicle [5-7].

FG consists of two components, a fibrinogen solution and a thrombin solution rich in calcium. When the two components are mixed, the thrombin enzymatically cleaves fibrinogen to form fibrin and factor XIII to factor XIIIa, which then crosslinks fibrin to form a gel. In the simplest formulation of fibrin glue as a drug delivery gel, exogenous drugs are added to one of the components before addition of the other, allowing the drug or factor to be distributed throughout the solution before cross linking. Since the amount of drug that can be loaded into FG has some limitations, methods to increase the efficacy of released anticancer agents are therefore of interest.

Photochemical internalization (PCI), a specialized form of photodynamic therapy (PDT) has been shown to improve the cytosolic delivery of drugs in a site-specific manner [8-10]. The basic principle for PCI is shown in Figure 1a and Figure 1b. Macromolecules that are internalized into cells via endocytosis end up inside and trapped in the intracellular endosomes and lysosomes (Figure 1a). The concept of PCI is based on using specialized photosensitizers, which localize in the cell membrane, are carried into the cell during the endocytotic event and remain in the endosome membrane, with the macromolecule trapped inside the endosome lumen. Upon light exposure the photosensitizer interacts with ambient oxygen to produce singlet oxygen. Since singlet oxygen has a very short range of action (< 20 nm), only the area of the vesicular membrane where the photosensitizer is localized will be damaged by singlet oxygen-mediated reactions with amino acids, unsaturated fatty acids and cholesterol in the membrane bilayer. The released agent can therefore exert its full biological activity, in contrast to being degraded by lysosomal hydrolases (Figure 1b).

PCI has been demonstrated to significantly enhance the efficacy of both bleomycin (BLM) and doxorubicin (DOX) [11-15]. In particular, PCI of BLM has been demonstrated to be effective as an adjunct to inadequate surgery and could significantly delay tumor re-growth in a mouse tumor model, compared to PDT or BLM treatment alone [16]. The combination of local intra-cavity FG slow-release drug delivery combined with PCI therefore has the potential of bypassing the BBB allowing increased chemotherapeutic efficacy.

The aim of the present in vitro research is designed to evaluate the ability of PCI to enhance the effectiveness of FG released drug on multi-cell 3-dimensional tumor spheroids formed from glioma tumor cells [17]. As opposed to cell monolayers, tumor spheroids more closely mimic in vivo tumors in their micro-environment in terms of gene expression and the biological behavior of the cells in tumors. Their 3-dimensional structure creates oxygen, nutrient, and pH gradients that result in quiescent cells which are more resistant to chemotherapy, ionizing radiation, and PDT/PCI. Spheroid cultures are therefore considered to be a realistic bridge between monolayer in vitro culturing and tumor work in vivo.

Materials and Methods

Cells

The rat glioma line (F98) was obtained from the American Type Culture Collection (Manassas, VA, USA) and were maintained in Dulbecco's Modified Eagle Medium (DMEM) with high glucose (Life Technologies Corp., Carlsbad, CA, USA) supplemented with 2% fetal bovine serum (FBS), 25 mM HEPES buffer (pH 7.4), penicillin (100 U mL^-1) and streptomycin (100 μg/mL^-1) at 37 °C and 5% CO₂.

Chemicals

The photosensitizer, aluminum phthalocyanine disulfonate (AlPcS_2a,) was obtained from Frontier Scientific, Inc. (Logan, UT, USA). The chemotherapeutic drugs Doxorubicin Hydrochloride (DOX) and Bleomycin (BLM) were obtained from Sigma Aldrich (St. Louis, MO, USA).

Fibrin glue and drug harvest

The fibrin glue was obtained from EMD Millipore Calbiochem (Temecula, CA, USA) and was composed of a 1:1 ratio of fibrinogen and thrombin, with drug or photosensitizer added to the thrombin. The 0.2 mL of the drug loaded thrombin was combined with 0.2 mL of fibrinogen in the wells of a 24 well microplate. The glue was allowed to gel for 20 min at 37 °C. The wells were washed twice to remove any free drug and 1.5 mL of drug-free culture medium was added to the well. The supernatant covering the FG layer was harvested from the wells after 2, 24, 48 or 72 hours by 2 different protocols. In the cumulative method (Figure 2a) four FG-drug wells were set up and the supernatants were collected for each time period from a separate well respectively. For the sequential method only (Figure 2b) one FG-drug well was made. The supernatant was collected after 2 hours of incubation and replaced by 1.5 ml of fresh medium and this process was repeated every 24 hours for a total of 72 hours.

Direct measurement of FG drug release

Fluorescence emission spectroscopy was performed to determine the relative concentrations of BLM and DOX in the supernatant. Measurements were carried out with a Cary Eclipse Fluorimeter, using a 1 cm quartz cuvette. For BLM, the excitation wavelength was set to 288 nm, which corresponds to the maximum absorption of the compound. Fluorescence emission was recorded between 300 nm and 500 nm, with the BLM emission maximum found at 345 nm. For DOX, the excitation wavelength was tuned to the absorption maximum at 484 nm, and fluorescence was recorded between 500 nm and 700 nm. DOX exhibits a characteristic fluorescence spectrum with a maximum near 600 nm. Relative concentrations of the drugs were determined for supernatant samples collected at different times by comparing the integrated fluorescence intensity near the emission maximum within a 10 nm bin.

Spheroid formation

A modified somewhat simplified method of that previously used [12] for spheroid formation was used in all experiments. F98 cells in suspension were incubated with AlPcS_2a, at 1 μg/mL for 2 hours, spun down and washed twice in medium to remove excess photosensitizer. The cells were used to form spheroids by a modification of the centrifugation method as previously described. Briefly, 2.5 × 10³ AlPcS_2a cells in 100 μL of culture medium per well were aliquoted into the wells of ultra-low attachment surface 96-well round-bottomed plates (Corning In.,NY). The plates were centrifuged at 1000 g for 30 minutes. Immediately following centrifugation, the tumor cells formed into a disk shape. The plates were maintained at 37 °C in a 5% CO₂ incubator for 24 hours to allow them to take on the usual 3-dimensionalspheroid form. The spheroids formed were uniform in size and were approximately 0.2 mm in diameter.

PCI

The basic FG-PCI experimental protocol is shown in Figure 2c. The formed spheroids were incubated together with 0.1 m of supernatant containing FG released drug collected at increasing times. For comparison purposes, spheroids were also cultured with BLM or DOX as pure drug at increasing concentrations ranging from 0-1.2 μg/mL for BLM and 0-0.1 μg/mL for DOX.

One hour after BLM, DOX or supernatant was added, light treatment, μ = 670 nm, from a diode laser (Intense; New Jersey USA) at an irradiance of 2.0 mW/cm² was administered for 8.0 or 10 min. corresponding to 0.96 or 1.2 J/cm² respectively.

Control cultures received either light treatment but no drug or FG supernatant (PDT control) or they received drug/FG supernatant but no illumination (drug-only control).

Following PCI or PDT, the plates were returned to the incubator. Typically, 8-16 spheroids were followed for each category, in three independent experiments, for up to 14 days of incubation. Culture medium in the wells was exchanged every third day. Determination of spheroid growth was carried out by averaging two measured perpendicular diameters of each spheroid using a microscope with a calibrated eyepiece micrometer and their volume calculated assuming a perfect sphere.

Statistical analysis

All data were analyzed and graphed using Microsoft Excel. The arithmetic mean and standard error were used throughout to calculate averages and errors. Statistical significance was calculated using the Student's t-test as well as the Welch's t-test. Two values were considered distinct when their p-values were below 0.05. Synergism was calculated when analyzing PCI treatments compared with drug or PDT alone. The equation $\alpha =\frac{S{F}^{PDT}\times S{F}^{drug}}{S{F}^{PCI}}$ was used to determine if the PCI effect was synergistic, antagonistic, or additive. α is defined as the ratio of the cumulative effect of 2 therapies, PDT and drug, administered independently to the net effect of combining the 2 therapies at a given dose. In this scheme, SF represents the survival fraction for a specific treatment. If 2 treatments are to be compared, the survival fractions of each separate treatment are multiplied together and then divided by the survival fraction when both treatments were applied together. The interaction is calculated based on the dose of each treatment. The resulting number (α) describes the summative effect as previously described [18]. If α > 1, the result is synergistic (supra-additive). If α < 1, the result is antagonistic, and if α = 1 the result is simply additive.

Results

PCI of BLM and DOX

In order to compare the effects on spheroid growth of BLM and DOX released from the FG layer experiments were performed, with and without PCI, using increasing concentrations of free BLM or DOX. The results are shown in Figure 3a and Figure 3b for increasing drug concentration and light dose for both drugs. Free drug-only experiments indicated that at concentrations ranging from 0 to 1.2 μg/mL for BLM and 0 to 0.1 μg/mL for DOX in the absence of light exposure, significant growth inhibition was seen only at the highest drug concentrations tested. On the other hand, the growth inhibitory effect of both drugs was significantly enhanced by PCI and was clearly synergistic for both BLM and DOX at the irradiance levels examined. The results of these experiments therefore act as standard calibration data that can be used to determin the concentration of FG released drug.

Direct determination of BLM and DOX release

The time course of the cumulative release from FG of BLM and DOX, as assayed by drug flourescence, is shown in Figure 4. The FG was loaded with 5 μg/mL of BLM or 1 μg/mL of DOX and the results are shown as a % of the maximum release. BLM release was more protracted (72 hours) compared to the release of DOX which reached a maximum after 48 hours.

Effects on spheroid growth of FG-BLM/DOX PCI

Cumulative supernatant harvest

Similar spheroid experiments as those described above for PCI for free BLM and DOX were performed employing supernatants containing released drug from loaded FG. The supernatants were harvested after 2, 24, 48 and 72 hours of incubation from 4 independent wells (Figure 2a). The results shown in Figure 5a, Figure 5b and Figure 5c represent spheroid growth following a 14 day period in culture. In the experiments shown in Figure 5a, 5 μg/mL of BLM were incorporated into the FG. PCI was done at a radiance of 1.2 J/cm². As seen in Figure 5a, in the absence of light treatment, the FG-BLM containing supernantants were not significantly inhibitory for spheroid growth for any of the harvest times examined. In contrast, spheroid growth inhibition was significantly enhanced by PCI. Significant growth inhibition was observed even by the supernatant harvested during the first 24 hours. Supernatants harvested after 48 and 72 hours showed only a slight non significant additional increase in PCI-mediated inhibitory effects.

Figure 5b shows light micrographs of F98 spheroids from a single experiment 14 days post-treatment. Although the spheroid exposed to FG released BLM in the absence of PCI as shown is slightly smaller than controls, this is a growth delay effect. Examining these spheroids two days later determined that they were of equal size compared to controls (data not shown). In contrast, the significant growth inhibition by FG-BLM-PCI using FG supernatants harvested after 24 hours is clearly demonstrated. The PCI treated spheroids are approximately the same size on day 14 as they were on day 2, indicating complete growth suppression.

The inhibitory effects of DOX, released from FG loaded with 1 μg/mL of the drug, weresignificantly inhibitory compared to non-treated controls for the harvest period of 24 hours (Figure 5c). For the 48-72 hour period the direct inhibitory effects decreased. This may have been due to a deterioration of the drug in the prolonged incubation in the presence of the FG layer. PCI of the released FG-DOX, as was the case for FG-BLM, significantly increased the inhibitory effects on spheroid growth at all of the harvest times. A slight decrease in FG-DOX PCI-mediated spheroid inhibition at the 72 hour harvest time paralled that seen for FG-DOX in the absence of PCI.

For both BLM and DOX the effects of PCI were clearly synergistic at all of the harvesting intervals. α values for both PCI of BLM and DOX were calculated from the data shown over the colums in Figure 5a and Figure 5c, Table 1. PCI of released drug harvested at 2, 24, 48 and 72 hours all resulted in α values greater than 1, indicating a significant synergistic response (p < 0.05).

In the sequential harvest method, the overlying medium is harvested after 2, 24, 48, and 72 hours and exchanged for fresh medium after 2, 24 and 48 hours as depicted in Figure 2b. The results shown in Figure 6a and Figure 6b represent spheroid growth following a 14 day period in culture. In the experiments shown in Figure 6a, 5 μg/mL of BLM were incorporated into the FG. PCI was done at a radiance of 1.2 J/cm². As shown in the figure, in the absence of light treatment (PCI), the FG-BLM containing supernantants were only slightly inhibitory for spheroid growth for the supernatant harvested after 2 hours. No inhibition of growh was seen for any of the harvest times examined compared to control cultures ( P > 0.1). In contrast, spheroid growth inhibition was significantly enhanced by PCI. Significant growth inhibition was observed by the supernatant harvested during the first 24 hours. Supernatants harvested after 48 and 72 hours showed no additional significant PCI-mediated inhibitory effects. In contrast, the inhibitory effects of DOX released from FG loaded with 1 μg/mL of the drug were signficanly inhibitory at the 24 hour harvest period, compared to non-treated controls. For all of the other harvest periods (Figure 6b) little effect of DOX could be demonstrated in the absence of light treatment. PCI of the released FG-DOX, significantly increased the inhibitory effects on spheroid growth for the first 48 hours of harvest. No growth inhibition with or without PCI was detected for the supernatants harvested after 72 hours indicating alow drug concentration.

Estimated FG-drug release

Using the data of the effects of free drug or FG-drug- PCI on spheroid growth shown in Figure 3, Figure 5, and Figure 6 the drug concentrations released from FG for both BLM and DOX can be estimated. The results for both harvest protocols (cumulative or sequential) can be seen in Figure 7a and Figure 7b. For the cumulative harvest protocol, FG-BLM supernatants harvested at 2 hours gave a spheroid volume reduced to approximately 35% of control values (Figure 5a). This is equivalent to that seen with a free BLM concentration of 0.15 μg/mL (Figure 3a). At FG-BLM harvested at 24, 48 and 72 hours, the concentration of BLM could be estimated at around 0.35 and 0.4-0.5 μg/mL respectively. Using the data from Figures 3b and Figures 5c, similar estimates for FG-DOX PCI gave a drug concentration of 0.055 and 0.095 μg/mL for FG-DOX supernatants harvested at 24 and 48 hours respectively with a slight decrease shown for the 72 hour harvest time. For the sequential harvesting protocol, assuming a FG-drug/supernatant equilibrium, the drug concentration in the FG layer will be reduced to 20% of its initial concentration for each medium exchange. This is clearly demonstrated for the time course of the estimated concentration of both drug (dashed lines Figure 7).

Discussion

Employing the cumulative supernatant harvest system used in these experiments, it is assumed that, after a sufficient incubation interval, an equilibrium drug concentration will be reached between the FG layer and the surrounding culture medium. In the experimental protocol used here, the drug containing FG layer was 0.4 mL in volume while the overlaying supernatant was 1.5 mL. It is assumed that the drug will slowly diffuse from the FG into the supernatant. At equilibrium, the final drug concentration in the supernatant would therefore represent approximately 20% (0.4/1.9 mL) of the initial drug concentration, corresponding to 1 μg/mL for BLM and 0.2 μg/mL for DOX, respectively. The maximum FG released drug concentrations shown in Figure 4 therefore probably represent these values. In addition, 0.1 mL of the supernatants were added to 0.1 mL in the well containing the spheroid, reducing the final theoretical maximum drug concentration influencing spheroid growth to 0.5 μg/mL for BLM and 0.1 μg/mL for DOX.

The results shown in Figure 4 (direct drug concentration) and Figure 7 (estimated drug concentration) although similar in time course are not identical. This is in all probability caused by the non-linear effect PCI mediated drug induced inhibition of spheroid growth as seen in Figure 3 for free drug. Increasing the drug concentration over a threshold level does not cause a related increase in spheroid growth inhibition. The increase in BLM concentration between 48 and 72 hours as shown in Figure 4 is therefore not reflected in the results shown in Figure 7a due to this "drug saturation" effect.

Although BLM and DOX are commonly used in a number of standard cancer therapies, they have been found to have limited use for the treatment of gliomas. Due to its hydrophilic nature and relatively large size, BLM has very limited penetration through the BBB and plasma cell membrane [19,20]. Although this is a clear disadvantage in terms of treatment efficacy, normal brain cells are protected from their toxic effects since these drugs would not retrograde re-enter the systemic blood stream. This contrasts with lipophilic chemotherapeutic agents like BCNU or TMZ, now in use clinically. Thus, BLM or DOX could be highly effective drugs for treatment of glioblastoma multiforme (GBM) in combination with local delivery strategies that increase the drug concentrations at the tumor site, bypassing the BBB and avoiding systemic side effects.

Enhanced efficacy of both BLM and DOX by PCI has been previously demonstrated on a variety of cancer cell types including glioma cells [12,14]. The data shown in Figure 5 and Figure 6 clearly indicate a significant increase in PCI-mediated FG-BLM or FG-DOX toxicity compared to either PDT or drug alone at the light levels and drug concentrations used. Due to its hydrophilic character, BLM is actively taken up into cells by endocytosis. Its poor ability to escape from endosomes leads to inactivation by hydrolytic enzymes and complexing molecules in secondary endosomes. In contrast, DOX in its neutral form is membrane permeable but relatively membrane impermeable in the acidic environment of lysosomes or recycling endosomes where it will be sequestered and inactivated within these intra-cellular compartments [21,22]. However, if released, these drugs quickly diffuse into the nucleus where they have a significant toxic effect. These characteristics make BLM or DOX well suited for use together with PCI, where the drug is selectively released from endosomal/lysosomal entrapment into the cell cytosol and nucleus.

PCI has been proven effective employing light treatment protocols either before or after drug administration [23,24]. In the case of DOX-PCI, it appears that the light before sequence is more effective than the light after [14,25]. In the experiments reported here, free or FG-released DOX was added to the cultures 24 hours after spheroid formation. Following a 1-hour incubation period, the initiation of light treatment was commenced. Since additional wash cycles were not used to remove any remaining DOX from the cultures, it is assumed that active drug was still available post-light treatment and therefore this protocol can be considered a combined light "after" and light "before" sequence. The pronounced synergistic effect of PCI-DOX on F98 spheroids was likely due to a combination of both facilitating its endo-lysosomal release (light after sequence) and by preventing lysosomal uptake of DOX (light before sequence).

Several other types of hydrogels besides FG have been studied for the local delivery and slow release of chemotherapeutic drugs in the tumor resection cavity for brain tumors in experimental animals [26]. In particular, Bastiancich and co-workers have developed a hydrogel made of lipid nanocapsules loaded with lauroyl-gemcitabine [4,27,28]. They have evaluated its effect in a resected GBM rat model and found that after local peri-surgical administration (in the resection cavity), the formation of recurrences of 9L tumors was delayed [27].

Fibrin glue though, has several characteristics that make it an attractive alternative to other forms of hydrogels. Firstly, thrombin and fibrinogen are naturally occurring substance in the coagulation process and are of low toxicity. FG has been used in surgical procedures for decades and is widely clinically approved. In addition, the parameters of the components can be modified to change the gel's structure, mechanical properties, and degradation [29]. FG is also easily molded to coat the walls of the resection cavity.

In the formulation of fibrin glue for chemotherapeutic agents used in cancer drug delivery, exogenous drugs are added to one of the components before addition of the other, allowing the drug to be distributed throughout the solution before cross linking, as was done in the experiments shown in Figure 4 and Figure 5. Although FG has been described for drug delivery for a variety of agents, it is the local release of chemotherapeutic drugs that is of interest here. Anai, et al. investigated FG as a drug delivery system for the local administration of Temozolomide (TMZ) in mice bearing subcutaneous tumors induced by the injection of malignant glioma cell lines. Slabs of gelled TMZ-containing FG were surgically placed in contact with the tumors. In mice treated with a combination of per-oral TMZ plus gelled FG-TMZ the tumors tended to be smaller than in mice treated with TMZ-FG or per-oral TMZ alone [7]. Furthermore, gelled FG-TMZ placed directly on the brain of living mice caused no significant tissue damage either in the acute or chronic phase. Although TMZ is extensively used in post-operative clinical treatment in patients, it was not evaluated in our study since it has been shown that its therapeutic effects are not significantly enhanced by PCI [30].

Formulations of fibrin glue can also include anti-fibrinolytic agents such as aprotinin to delay or slow fibrinolysis, which in turn would lead to slower drug release [31,32]. Yoshida, et al. demonstrated that the release of 5-FU and mitomycin were released relatively rapidly, independent of aprotinin, compared to enocitabine where drug release was slowed in the presence of aprotinin [5].

In all probability, the release profile of DOX and especially BLM seen in the experiments reported in the present study would benefit if prolonged past the 48-hour time point. Kitazawa, et al. examined the release kinetics of DOX from FG or a composite gel of fibrin with sodium alginate [33]. The in vitro mean release times of DOX from FG and FG containing sodium alginate were 8.7 hours, and 81 hours, respectively. This clearly indicated a significant sustained release of DOX in the presence of sodium alginate. All in all, these previously reported studies clearly illustrated the potential of fibrin glue as a carrier for combined localized delivery systems such as drugs, nanoparticles or composite gels.

The combination of intra-cavity FG or hydrogel slow-release drug delivery combined with PCI therefore has the potential of by passing the BBB in a targeted confined area thus allowing increased chemotherapeutic efficacy while reducing treatment side effects. This approach can be readily translated to in vivo animal experiments and since FG is widely clinically approved, eventually to patient treatment protocols (Figure 8). As shown in Figure 8, following tumor resection, the resection cavity is coated with drug/photosensitizer loaded FG. The FG slowly dissolves releasing the drug. Light treatment is done through a balloon applicator implanted during the initial cytoreductive surgery and positioned in the center of FG lined resection cavity. Indwelling light/radiation applicators have been temporarily implanted in resection cavities during surgery, remaining in place for up to one week before removal [34-36].

Conclusion

The results of the present study show that active drug was released from FG layers for an extended time period. The growth inhibition caused by either FG released BLM or DOX was significantly enhanced by AlPcS_2a mediated PCI. AlPcS_2a, released from FG, together with light treatment could also provide for effective PDT.

Funding

The Norwegian Radium Hospital Research Foundation. Grant nr. SE. 1305/1503.

Conflict of Interest

All of the authors declare that she/he has no conflict of interest.

Ethical Approval

This article does not contain any studies with human participants or animals performed by any of the authors.

Acknowledgments

The authors are grateful for the support from the Norwegian Radium Hospital Research Foundation.

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