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The aim of this study is the development of a three-dimensional multicellular spheroid cell culture model for the longitudinal comparative and large-scale screening of cancer cell proliferation with noninvasive molecular imaging techniques under controlled and quantifiable conditions.
The human glioblastoma cell line Gli36ΔEGFR was genetically modified to constitutively express the fluorescence protein mCherry, and additionally labeled with iron oxide nanoparticles for high-field MRI detection. The proliferation of aggregates was longitudinally monitored with fluorescence imaging and correlated with aggregate size by light microscopy, while MRI measurements served localization in 3D space. Irradiation with γ-rays was used to detect proliferational response.
Cell proliferation in the stationary three-dimensonal model can be observed over days with high accuracy. A linear relationship of fluorescence intensity with cell aggregate size was found, allowing absolute quantitation of cells in a wide range of cell amounts. Glioblastoma cells showed pronounced suppression of proliferation for several days following high-dose γ-irradiation.
Through the combination of two-dimensional optical imaging and 3D MRI, the position of individual cell aggregates and their corresponding light emission can be detected. This allows an exact quantification of cell proliferation, with a focus on very small cell amounts (below 100 cells) using high resolution noninvasive techniques as a well-controlled basis for further cell transplantation studies.
When transgenic cell lines are generated with expression of imaging reporters and additional labeling for magnetic resonance imaging (MRI), their proliferation characteristics need to be investigated under well-defined control conditions before in vivo transplantation experiments which enable detailed understanding of in vivo processes. In the past, such investigations have been performed on monolayer cultures. However, a three-dimensional cell aggregate system is preferable allowing a more realistic characterization of cell dynamics and complex pathophysiological responses to (therapeutic) interference with proliferation. Formation of multicellular aggregates has been reported for different cell types and tissues in vitro without loss of tissue-like characteristics . This culture form resembles functional tissue properties better than two-dimensional culture variants. Recent advances in 3D spheroid research include new functional methods like biochip-based culture systems for high-throughput drug screening . In the field of imaging research, the identification, observation, and exact quantification of variable and very small cell amounts (below 100 cells) is an emerging topic.
Molecular imaging is a very sensitive and versatile tool for the detection of different kinds of cells and of cellular characteristics with wide application in tumor biology. Whole body imaging techniques, either fluorescence, bioluminescence, or magnetic resonance, provide powerful tools for noninvasive, longitudinal monitoring of tumor cell progression in small animal in vivo models . The combination of optical imaging techniques with high-field MRI generates a synergy provided by the high sensitivity of optical imaging and the high, three-dimensional resolution of MRI , resulting in the detectability of cells within an object. Cells can be labeled intracellularly by endocytosis of superparamagnetic particles containing iron oxide, coated by a polymer or polysaccharide shell . The iron oxide nanoparticles effectively shorten the transverse relaxation time T2 of protons through susceptibility-induced local magnetic field inhomogeneities, resulting in hypointensity contrast in T2-weighted MR images . The overall diameter of particles used for cell labeling studies ranges from 30 nm up to or even larger than 1 µm .
High-grade malignant glioblastoma is one of the most common primary tumors of the central nervous system and is characterized by highly extensive tissue infiltration and high proliferation rates. Due to its aggressiveness the mean survival time of patients is less than 12 months [1–3]. The glioblastoma cell line Gli36ΔEGFR, formerly established by retroviral transfer of a mutant epidermal growth factor receptor (EGFR) into the Gli36 glioblastoma cell line , was chosen as the model cell line for our in vitro investigation on cell proliferation under controlled conditions. ΔEGFR-transduced tumor cells are excellent models for in vivo applications because of their rapid growth in rat brains . We introduced the fluorescent protein mCherry under control of the cytomegalovirus promoter, resulting in a strong expression of this optical imaging reporter. Additionally, the cells were labeled with the clinically used MRI iron oxide contrast agent Endorem, producing a pronounced T2*-weighted contrast.
In the present study, we report establishment of a cell aggregate model which is suitable for a detailed and longitudinal characterization of glioma cell proliferation and for large-scale screening purposes under controlled conditions in vitro. For this purpose, we have developed a three-dimensional, agarose-based in vitro cell model, while applying combined imaging techniques for complementary information content. It was the aim of the study to use optical imaging (fluorescence in the present case) and phase contrast microscopy for the sensitive detectability of small cell clusters and achieve the quantification of even small cell aggregates. High-field MRI was chosen for precise three-dimensional localization of the selected cell aggregates. We have deliberately chosen to set up a cell aggregate model for our investigation of tumor cell behavior as these aggregates represent a more complex cellular model, compared to a monolayer-culture model. To demonstrate the exemplary potential of this cell model, the evaluation of cancer treatment strategies was investigated monitoring the response of tumor cell aggregates to γ-ray exposure.
Gli36ΔEGFR human glioblastoma cells [7, 8] were kindly provided by A. Jacobs (MPI for Neurological Research, Cologne). Cells were maintained in Dulbecco’s modified eagles medium, supplemented with 10% fetal calf serum (FCS), penicillin (100 U ml−1), streptomycin (100 µg ml−1), and 200 µM l-glutamine (all reagents from PAA, Pasching, Austria) on cell culture dishes (Greiner, Frickenhausen, Germany). All cells were maintained in 5% CO2 and 90% humidity at 37°C.
The fluorescence reporter mCherry was kindly provided by R. Tsien (University of California, San Diego, CA, USA). The mCherry containing plasmid was treated with BamHI and EcoRI (New England Biolabs, Ipswich, USA) and introduced into the expression vector pcDNA3.1(+) downstream of the cytomegalovirus promoter (Invitrogen, Karlsruhe, Germany). Glioblastoma cells were transfected using the lipofection agent Metafectene (Biontex Laboratories, Martinsried, Germany) and 1 µg of the purified plasmid for 4×105 cells. Further selection was performed with the supplementation of 400 µg ml−1 neomycin (PAA). For the generation of a homogeneous population, single cells were cultured in 96-well plates (Greiner) and screened for fluorescence intensities. Clone number 17 was chosen for the following experiments because of its high mCherry fluorescence.
For the formation of the cellular aggregates, cells were cultured on cell culture dishes coated with Poly(2-hydroxyethyl methacrylate) (Poly-HEMA, Sigma-Aldrich, Taufkirchen, Germany) preventing attachment to the surface. The cells were labeled by co-incubation with the clinically used MRI contrast agent Endorem® (Guerbet, Roissy, France) consisting of small superparamagnetic iron oxide particles with a mean diameter of 150 nm and a total iron content of 11.2 mg ml−1  during the spontaneous aggregate formation. Incubation with 112 µg ml−1 or 224 µg ml−1 Endorem was performed for 24 h in a total volume of 1 ml FCS-containing medium and 4×105 cells. At the end of the labeling experiment, cells were washed three times with phosphate-buffered saline (PBS) without Ca2+ and Mg2+ (PAA), and centrifuged at 16×g in 15-ml tubes. Aggregates were suspended in FCS-containing medium without phenol red (Invitrogen) and either plated for 3 h on Poly-l-ornithine and 1 µg ml−1 fibronectin (Sigma-Aldrich) coated cover slips for Prussian blue staining and immunocytochemistry or for incubation experiments in low-melting agarose (Sigma-Aldrich) phantoms. We used 35 mm diameter dishes equipped with a 2 mm bottom grid for colocalization purposes (Thermo Fisher Scientific, Langenselbold, Germany). For the imaging experiments, aggregates were seeded in low-melting agarose and overlayed with FCS-containing cell culture medium. In some staining experiments aggregates were placed on treated four-well chamber slides (Becton Dickinson, Heidelberg, Germany).
For the determination of a potential influence of the MRI contrast agent on the fluorescence measurement, 1×105 cells were cultured in 24-well plates (Greiner) in the presence of 112 or 224 µg ml−1 Endorem. Fluorescence analysis was performed 24 h after the initial supplementation and further washing steps in a multimode reader (Mithras LB 940, Berthold Technology, Bad Wildbad, Germany).
Fixation of aggregates cultured on cover slips was performed for 25 min with a 4% paraformaldehyde solution at room temperature, and agarose embedded aggregates were fixated for 24 h at 4°C. After permeabilization with 0.25% Triton X-100 (Fluka, Taufenkirchen, Germany) and further incubation with a 5% bovine serum albumin (Fraction V Cohen, PAA) cells were incubated with the primary antibodies anti-vimentin (mouse; 1:1,000, Sigma Aldrich), and FITC coupled anti-dextran (1:25, clone DX1, Stem Cell Technologies, Vancouver, Canada). For anti-vimentin antibody detection, the secondary antibody anti-mouse 488 (Thermo Fisher Scientific) was used. Nuclei were detected with the bisbenzimide Hoechst Dye 33342 (1:1,000, Sigma Aldrich) or with Sytox green (1:1,000, Invitrogen) after 10 min incubation. The glass cover slips were embedded with Aquamount (Polyscience Inc., Eppelheim, Germany) and further processed.
Fluorescence and confocal microscopy were performed on a Leica Laser scanning microscope (LSM) equipped with a supplementary CCD-camera (Leica, Wetzlar, Germany). Phase contrast microscopy was recorded on a Zeiss Axiovert microscope (Zeiss, Goettingen, Germany). For the determination of the aggregate diameter, the minimal and maximal in-plane diameters of each multicellular aggregate were measured with phase contrast microscopy and coregistered with the fluorescence images. The mean diameter of the two was used for the volume calculation.
For the detection of iron, cells were treated with a diaminobenzidine (DAB) enhanced Prussian blue staining. Cells were fixated, washed in PBS, and incubated for 30 min in a 1:1 ratio solution with 2% potassium ferrocyanide (Perl’s reagent, Merck, Darmstadt, Germany) and 2% HCl, followed by 10 min DAB treatment (Sigma-Aldrich) according to the manufacturer’s protocol.
Fluorescence imaging was performed with the real-time fluorescence and bioluminescence small animal optical imaging system, Photon Imager (Biospace Labs, Paris, France), equipped with a custom-manufactured platform including four glassfibers for optimal illumination of the cell culture sample. Fluorescence light exposure time was 30 s, the filters were set for emission at 610 nm and excitation at 585 nm. Aperture was set to 2.8. The optical imaging experiments of the 35 mm cell culture dishes were performed with open lids to reduce reflections.
All magnetic resonance imaging experiments were performed on a Bruker Biospec 11.7 T dedicated animal scanner (Bruker BioSpin, Ettlingen, Germany) with a 16 cm horizontal bore magnet, equipped with actively shielded gradients (750 mT m−1). A transmit–receive radiofrequency coil with a 45 mm diameter was used. Three-dimensional high-resolution T2*-weighted MR images were acquired using a gradient echo sequence (FLASH, TR=100 ms, TE=5 ms, or TE=18 ms, flip angle 30°; 12 averages). The field-of-view was 36×37×5 mm3 with a matrix size of 512×512×64, resulting in an almost isotropic spatial resolution of 70×74×78 µm.
Cell systems were irradiated by high-energy photon radiation, generated by an electron linear accelerator (Type SL 75/5, Elekta, Crawley, GB). High energetic electrons are decelerated by a tungsten target, thereby producing bremsstrahlung of 5 MeV energy at maximum. The radiation field was 20×20 cm, ensuring a homogeneous dose distribution across the whole sample holder. The distance between sample and radiation source was 100 cm. Additionally, 2 cm of polymethyl methacrylate were positioned directly above the samples in order to eliminate the build-up effect. The agarose-based cell systems were irradiated with 20 and 50 Gy, respectively. Control cell systems without treatment were placed outside the treatment room during activation of the beam. After radiation exposure photon flux was determined over a time period of 6 days. In these experiments the fluorescence excitation intensity was reduced to 50%.
Optical imaging experiments were analyzed with the software package PhotovisionPlus (Biospace Labs, Paris, France) and NIH imageJ. MRI images were processed using Paravision 4 (Bruker BioSpin, Ettlingen, Germany). 3D reconstruction was performed with the software package Amira (version 3.1, Mercury Computer Systems, Inc., Chelmsford, USA).
Statistical analysis was performed with Origin software package, version 8 (OriginLab Corporation, Northampton, USA).
Culturing cells in the presence of two different concentrations of the MRI contrast agent Endorem on an anti-adhesive surface leads to an aggregate formation with minimal diameters ranging between 10 and 60 µm, as well as single cells. For detection of iron oxide particles in cells and for assessment of the integrity of the cytoskeleton after uptake of superparamagnetic particles, aggregates were placed for 3 h on a Poly-l-ornithine and fibronectin-coated surface (Fig. 1). The anti-dextran antibody staining shows a remarkable uptake of contrast agent particles in the cytoplasm as well as iron containing beads attached to the outer membrane surface of cells (Fig. 1c). Also, a clustering of the nanometer-sized particles could be observed. Single cells that migrated away from the aggregate center during the culturing period had intact, vimentin-positive intermediary filaments, and the mCherry protein was located in the cytoplasm as well as in the cell nucleus. Complementary to fluorescence microscopy, achieved with anti-dextran antibody for nanoparticle detection, Prussian blue staining (Fig. 1d) was performed to reveal the presence of iron with light microscopy: iron containing particles were found to be distributed inside the cells, but with a variation of quantitative uptake of particles. This variability was observed also in monolayer cultures after exposure to the contrast agent (data not shown). We therefore do not believe that such an inhomogeneous distribution is due to the chosen aggregate culture technique.
Cells, cultured as a monolayer and labeled for 24 h with two different concentrations of Endorem, showed the same mCherry fluorescence light intensity, independent of the supplemented contrast agent concentration (Fig. 2). Thus, additional incorporation of the MRI contrast agent does not lead to any fluorescence quenching effect.
After placing multicellular aggregates in an agarose-based matrix, enriched with serum-containing medium, photon emission of these phantoms was registered with the optical imager after excitation at 585 nm for 30 s (Fig. 3a), followed by recording of T2*-weighted 3D MRI scans (Fig. 3b). All of the stationary aggregates were detected and co-localized with these two independent imaging techniques. Due to the 3D capability of MRI, the position of the cell aggregates could also be discriminated along the third dimension (Fig. 3c).
For multimodal imaging coregistration, regions of interest were selected and analyzed (Fig. 4). Fluorescence imaging and phase contrast microscopy, performed for the analysis of minimal aggregate diameter, were determined (Fig. 4a, b). In a comparative analysis between two different T2*-weighted echo times (TE=5.0 and 18.0 ms; Fig. 4c, d), each aggregate was clearly visible and could be coregistered with the microscopic pictures and the fluorescence images. Additionally, a 3D model of the aggregates (Fig. 4e), based on the MRI data of the 5 ms TE scan (Fig. 4c), displays the localization of cells at variable depths in the agarose phantom.
Photon flux and measured in-plane diameters of various aggregates were determined from 200 randomly selected multicellular aggregates in 14 independent phantoms. This led to an excellent linear correlation (regression coefficient R=0.9) between estimated aggregate volume and fluorescent light intensity, as shown in Fig. 5. Fluorescent light intensity (FI) was found to depend on cluster volume with the following equation:
where V is the volume of the cell aggregate under consideration. This volume was calculated from the measured cell aggregate diameter under the assumption of a perfect spherical cell distribution of the aggregate. In a small sampling study, we correlated the absolute cell number, determined with confocal laser scanning microscopy, with the photon flux, measured by the optical imager. The smallest detectable cell amount, clearly discriminated from the fluorescent background signal, was five cells. The relation between the fluorescent signal intensity and the cell number also follows a linear function (data not shown).
Cells were cultured for a time period of 5 days in an agarose-based, growth factor enriched matrix. Each day, photon flux and diameter of the aggregates (by light microscopy; see above) were determined (Fig. 6). A representative analysis of the photon flux of four aggregates with different diameters at the beginning of observation displays the proliferation of the selected stationary cell clusters (Fig. 6c). The diameter of the smallest of the four selected aggregates increased from 49.5 µm at the beginning to 121.75 µm after 120 h. The aggregate with an initially larger diameter of 76.75 µm showed a diameter of 176.75 µm at the termination of the experiment.
To investigate cancer therapy with γ-irradiation in vitro under controlled conditions, cellular aggregates were exposed to doses of 20 and 50 Gy, respectively, at 24 h after setting up the cell culture. For the determination of radiation-induced effects the phantoms were cultured for the following 6 days. During this observation period, fluorescent light intensity was determined from a series of cell aggregates. At 24 h after irradiation, a slight decrease in photon flux was noted (Fig. 7). Proliferation of treated aggregates came to an almost complete halt, with a minute increase at the time point 90 h after seeding. After this time, a small decrease in photon flux was observed, indicating a slow but continuous loss of cells. Determination of aggregate diameters at the termination of the experiment led to a proliferative volume increase to 238%±48% in the non-irradiated control group, when compared to the initial diameter at the experimental start. During the same observation period, the photon flux of the 20 Gy irradiated phantoms increased to 128%±10%, and for the cells treated with 50 Gy to 122.6%±48.8% of the initial volume. The growth characteristics of the untreated control aggregates corresponded to the values obtained in proliferation experiments, visualized in Fig. 6.
We have developed a stationary cell model system for the in vitro monitoring and quantification of cell dynamics. This model allows observation of cell proliferation under controlled conditions while assuring the cellular viability. Consequently, this opens the way for longitudinal studies with multiple measurements using even complementary imaging techniques. As these imaging techniques are also applicable for in vivo investigations, in vitro results have a clear translational potential. To our knowledge, this is the first description of a cell model system in which continuous monitoring of cellular characteristics over time and functional allocation to specific cell amounts is achieved with a novel multimodal imaging approach.
Bioluminescence is the most commonly used in vivo imaging modality for signals coming from cells deep in the tissue. Available fluorescence reporters, on the other hand, especially GFP and EGFP, have serious limitations concerning the tissue penetration depth and because of severe autofluorescence contributions . The red fluorescence protein and its even more red-shifted variants such as the mCherry protein from the fruit series , as well as the development of near-infrared dyes have longer excitation and emission wavelengths, thereby decreasing the contribution of autofluorescence substantially. More important, tissue penetration depth of light is substantially increased to deeper layers using these red-shifted probes for their lower tissue absorption and light scattering . In the present investigation, the Gli36ΔEGFR cells, displaying a highly invasive phenotype and characterized by rapid proliferation [7, 8], were transfected to express the fluorescence imaging reporter mCherry. We selected a clone with a mCherry expression 3.5 times stronger than the average value of the original neomycin-resistant mCherry-positive population. Exclusively, this cell line with the strong and stable mCherry expression was used for further experiments to assure maximal fluorescence detection sensitivity.
For the MRI experiments, incubation with a concentration of 112 or 224 µg ml−1 Endorem for a time period of 20 h was found sufficient for detection of labeled cells by MRI. Detectability of small cell clusters was found to be variable in each separate sample preparation due to a nonhomogeneous uptake of the superparamagnetic particles among cells. Detectability of proliferating, growing cell clusters, on the other hand, was not observed to be compromised by proliferation-dependent dilution of the MRI label. As the clusters grow due to their proliferation, larger, compact cell aggregates arise, commonly easier visualized on MRI images. Detectability of labeled stem cells as a function of their proliferation was recently reported from our lab . There it was found that a dilution factor of 256 (equivalent to a label dilution due to eight cell generations of proliferative duplication) still results in a clearly detectable MRI contrast in vitro.
One difficulty with in vitro MRI is the determination of the number of labeled cells from the experimentally observed T2 or T2* signal decrease in a sample. Cell labeling with large particles (several hundred nanometers up to 1 µm) increases the MRI contrast enhancement through greater amounts of iron per particle but possesses a reduced cellular labeling efficiency compared to particles with a diameter around 100 nm . One possibility to measure a small amount of cells or even single cells is to produce a highly diluted agarose-cell solution, in which the single hypointense spots on the MR images represent single cells (or small clusters thereof) serving direct cell quantification [14, 15]. Culture of cells and multiple MRI measurements provides detailed information about cellular activity and behavior. Therefore, growth and invasion characteristics of multicellular melanoma tumor spheroids with larger diameters were analyzed in agarose gels . A recent publication from Huang and colleagues describes the expansion dynamics of glioma cells embedded in gadolinium–DTPA enriched collagen I over the time period of 12 h with high spatial resolution . These cells were not previously labeled with an MRI contrast agent, which would, however, be a necessary prerequisite for further in vivo transplantation experiments. Bernas et al. labeled C6 rat glioma cells with fluorescent, iron-containing particles that had a mean diameter of 0.9 µm . Labeled cells in this study were cultured for up to 8 days, allowing to invade into a collagen I matrix, and further analyzed with a 1.5 T MRI and corresponding phase contrast microscope. All the above cited studies have some limitations in common concerning their labeling techniques. Large amounts of nanometer-sized particles are necessary for efficient and robust detection of small cell amounts, but homogeneous, equal labeling of all cells is not guaranteed. A further problem is a dilution process of the iron oxide particles with each cell division, leading to contrast agent dilution, possibly even beyond detectability . Therefore, quantification of the exact cell amount in a longitudinal study is problematic with these MRI label-based methods.
We chose a stationary proliferation model allowing multicellular aggregates to proliferate and to be analyzed with different multimodal imaging techniques with the focus on the detectability and colocalization. This allows a rapid screening and identification of multicellular clusters while observing individual cell cluster dynamics in longitudinal studies. Stable expression of the fluorescence marker mCherry allows determination of the exact cell number in a sample with high sensitivity, without problems due to contrast agent dilution effects and inhomogeneous uptake. We calculated, based on confocal LSM, the minimal detectable cell amount of various cell clusters and found a linear correlation to the photon flux (K. Kruttwig et al., unpublished results). For larger cell amounts and fast screening of the samples, it is useful to determine the microscopic cluster diameter instead of the absolute cell amount, as the latter approach requires time-consuming laser scanning microscopy. The optical microscopic methods are limited by axial resolution and working distances of the objectives [18, 20]. Fluorescence imaging is a rapid method for the detection of small amounts of living cells with high sensitivity , but without in-plane high resolution and without information about the axial distribution. As seen in Fig. 6 for larger cell aggregate volumes, the experimental data deviates slightly from the linear behavior for larger cell cluster volumes. This is indication that the assumption of a perfectly spherical volume no longer holds for large cell clusters which will spread out to reach more and more a disk-shaped volume. Here, three-dimensional information about the axial cell distribution will come in handy: high-resolution MRI provides the possibility to acquire 3D data sets with resolution of 100 µm or better , but at the expense of longer measurement periods compared to photon imaging. The cells were detected and quantified with fluorescence imaging (at a scan time of 30 s), and were visualized with a resolution of 70 µm with MRI. Where necessary, further 3D image reconstruction based on the MRI data could be added for detailed localization issues. As shown in Figs. 3, ,4,4, and and6,6, it is easily possible to discriminate the aggregates with both imaging techniques with high resolution and in longitudinal studies.
A radiation induced decrease of cell proliferation of the human glioblastoma cell line was observed after irradiation with lethal dosages of either 20 or 50 Gy. This was visualized with quantitative fluorescence imaging. Glioblastoma cells are known to show a markedly augmented radioresistance to radiation therapy strategies and often respond with an enrichment of a CD133+ cancer stem cell population [21, 22]. After irradiation with sublethal doses an enhancement of migrational activity and infiltration has been reported .
In a recently published study from Thorsen et al. , a specially designed dish for radiosurgery of human glioma spheroids in suspension was used for irradiation with 12 or 24 Gy using a gamma knife. These authors reported a dose-dependent inhibition of tumor growth after irradiation, observed with microscopic techniques. The radiation effects on the tumor growth of pretreated tumor cells was assessed by MRI after xenotransplantation into the nude rat brain.
The combination of both imaging techniques for the application to our in vitro cell model system provides an ideal tool for rapid noninvasive monitoring of the cell dynamics of large amounts of tumor cells (in various cell aggregates). This investigation procedure therefore makes the cell system useful for the assessment of cancer treatment efficiency by using proliferational activity as the evaluation criterion. In principle, cell clusters with different response behavior to a treatment modality (e.g. radiation) can be identified and analyzed separately to better understand involved pathomechanisms.
Additional transfection of the cells with luciferase to allow use of bioluminescence imaging can be an additional method to monitor and quantify metabolically active cells due to the ATP dependence of the enzymatic reaction [25–27]. Compatibility of the agarose model with such vitality marker strategy has already been demonstrated in a proof-of-principle experiment in our laboratory (K. Kruttwig, unpublished).
We have developed a stationary cell model system, allowing observation of viable cellular dynamics, compatible for longitudinal studies. The fluorescence imaging method has been calibrated demonstrating a linear correlation between fluorescence intensity and volume of the cell aggregates based on light microscopy and photon flux determination. This now permits characterization of the cell aggregate dynamics in a quantitative manner in vitro with noninvasive imaging techniques. Direct application to radiation treatment of the human glioblastoma cell model, used in our present investigation, shows that a sensitive recording of radiation-induced proliferation modulation is possible with this cell model system. On a more general level, the here described setup can be applied to systematic characterization of cell line behavior under different conditions, and can be exploited to assess efficiency of treatment strategies under controlled in vitro conditions, while at the same time understanding contributing (patho-)mechanisms better.
We thank Michael Diedenhofen for excellent technical assistance with the image coregistration, and Jan Jikeli for help with the growth curve fits. We thank the Company Biospace for manufacturing the custom-built illumination platform. Generous supply of Endorem by Drs. C. Corot and P. Robert (Guerbet, France) is gratefully acknowledged. This study was supported by a grant from the Volkswagen-Stiftung, and by grants from the EU-FP6 program: DiMI (LSHB-CT-2005-512146) and EMIL (LSHC-CT-2004-503569).
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