The dependency of compound biological effectiveness factors on the type and the concentration of administered neutron capture agents in boron neutron capture therapy
© Masunaga et al.; licensee Springer. 2014
Received: 12 December 2013
Accepted: 20 February 2014
Published: 7 March 2014
To examine the effect of the type and the concentration of neutron capture agents on the values of compound biological effectiveness (CBE) in boron neutron capture therapy.
Methods and materials
After the subcutaneous administration of a 10 B-carrier, boronophenylalanine- 10 B (BPA) or sodium mercaptododecaborate- 10 B (BSH), at 3 separate concentrations, the 10 B concentrations in tumors were measured by γ-ray spectrometry. SCC VII tumor-bearing C3H/He mice received 5-bromo-2′-deoxyuridine (BrdU) continuously to label all intratumor proliferating (P) cells, then treated with BPA or BSH. Immediately after reactor neutron beam irradiation, during which intratumor 10 B concentrations were kept at levels similar to each other, cells from some tumors were isolated and incubated with a cytokinesis blocker. The responses of BrdU-unlabeled quiescent (Q) and total (= P + Q) tumor cells were assessed based on the frequencies of micronucleation using immunofluorescence staining for BrdU.
The CBE values were higher in Q cells and in the use of BPA than total cells and BSH, respectively. In addition, the higher the administered concentrations were, the smaller the CBE values became, with a clearer tendency in the use of BPA than BSH. The values for neutron capture agents that deliver into solid tumors more dependently on uptake capacity of tumor cells became more changeable.
Tumor characteristics, such as micro-environmental heterogeneity, stochastic genetic or epigenetic changes, or hierarchical organization of tumor cells, are thought to partially influence on the value of CBE, meaning that the CBE value itself may be one of the indices showing the degree of tumor heterogeneity.
A neutron capture reaction in boron [ 10 B(n, α) 7 Li] is, in principle, very effective in destroying tumors, provided that a sufficient amount of 10 B can be accumulated in the target tumor and a sufficient number of very-low-energy thermal neutrons can be delivered there. The two particles generated in this reaction have a high linear energy transfer (LET) and have a range of roughly the diameter of one or two tumor cells. It is theoretically possible to kill tumor cells without affecting adjacent healthy cells, if 10 B atoms can be selectively accumulated in the interstitial space of tumor tissue and/or intracellular space of tumor cells. Thus, successful boron neutron capture therapy (BNCT) requires the selective delivery of large amounts of 10 B to malignant cells (Barth et al.2005).
The greater density of ionizations along high LET particle tracks results in an increased biological effect compared with the same physical dose of low LET radiation. This is called relative biological effectiveness (RBE), which is the ratio of the absorbed dose of a reference source of radiation (e.g., X-rays) to that of the test radiation that produces the same biological effect. Because both tumor and surrounding normal tissues are present in the radiation field, there will be an unavoidable, nonspecific background dose, consisting of both high and low LET radiation. However, a greater concentration of 10 B in the tumor will result in receiving a much higher total dose than that of adjacent normal tissues. This is the basis for the therapeutic gain in BNCT. The total radiation dose delivered to any tissue can be expressed in photon equivalent units as the sum of each of the high LET dose components multiplied by weighting factors, which depend on the increased radiobiological effectiveness of each of these radiation components (Barth et al.2012).
The dependence of the biological effect on the microdistribution of 10 B requires the use of a more appropriate term than RBE to define the biological effects through the 10 B(n,α) 7 Li reaction. Measured biological effectiveness factors for the components of the dose from this reaction have been originally introduced by Gahbauer et al. as the “compound factors” (Gahbauer et al.1989; Gupta et al.1994). Subsequently, the factors have been called “compound biological effectiveness (CBE) factors” (Hopewell et al.2011; Hopewell et al.2012). The mode and route of the administration of a 10 B-carrier, the 10 B distribution within the tumor, normal tissues, and even more specifically within cells, and even the size of the nucleus within the target cell population, can all influence the experimental determination of the CBE factor. CBE factors are fundamentally different from the classically defined RBE, which is primarily dependent on the quality (i.e., LET) of the radiation administered. CBE factors are strongly influenced by the distribution of the specific 10 B delivery agent and can differ substantially, although they all describe the combined effects of α particles and 7 Li ions. The CBE factors for the 10 B component of the dose are specific for both the 10 B delivery agent and the tissue. A weighted Gy unit [Gy(w)] has been used to express the summation of all BNCT dose components and indicates that the appropriate RBE and CBE factors have been applied to the high LET dose components. However, for clinical BNCT, the overall calculation of photon equivalent [Gy(w)] doses requires several assumptions about RBEs, CBE factors, and the 10 B concentrations in various tissues, based on currently available human or experimental data (Hopewell et al.2011; Hopewell et al.2012).
Here, we tried to analyze the changes in the values of RBE for neutron only irradiation and CBE factors for employed 10 B-carriers according to their concentrations when administered in vivo. The neutron capture reaction was performed with two 10 B-carriers, boronophenylalanine- 10 B (BPA, C 9 H 12 10 BNO 4 ) and sodium mercaptoundecahydrododecaborate- 10 B (sodium borocaptate- 10 B, BSH, Na2 10 B 12 H 11 SH). Regarding the local tumor response, the effect not only on the total (= proliferating (P) + quiescent (Q)) tumor cell population, but also on the Q cell population, was evaluated using our original method for selectively detecting the response of Q cells in solid tumors (Masunaga and Ono2002).
Materials and methods
Mice and tumors
SCC VII squamous cell carcinomas (Department of Radiology, Kyoto University) derived from C3H/He mice were maintained in vitro in Eagle’s minimum essential medium supplemented with 12.5% fetal bovine serum. Cells were collected from exponentially growing cultures, and 1.0 × 105 cells of each tumor were inoculated subcutaneously into the left hind legs of 8- to 11-week-old syngeneic female C3H/He mice (Japan Animal Co., Ltd., Osaka, Japan). Fourteen days after the inoculation, each tumor had reached approximately 1 cm in diameter. At treatment, the body weight of the tumor-bearing mice was 22.1 ± 2.3 (mean ± standard deviation) g. Mice were handled according to the Recommendations for Handling of Laboratory Animals for Biomedical Research, compiled by the Committee on Safety and Ethical Handling Regulations for Laboratory Animal Experiments, Kyoto University. All experimental procedures mentioned here were in accordance with institutional guidelines for the care and use of laboratory animals in research.
BPA and BSH were purchased from Katchem spol. s.r.o. (Czech Republic). BPA was converted to a fructose complex to increase its solubility following the method reported by Coderre et al. (Coderre et al.1994). The aqueous solution of BPA was prepared at a concentration of 250, 500, or 750 mg·kg −1 . BSH dissolved in physiological (0.9%) saline was prepared at a concentration of 125, 250, or 375 mg·kg −1 . In accordance with our previous studies (Masunaga et al.2001), at a dose of less than 1,500 mg·kg −1 for BPA and less than 500 mg·kg −1 for BSH, no overt toxicity was observed. Based on the certificate of analysis and Material Safety Data Sheet provided by the manufacturer, it was not contaminated with the borocapatate dimer (BSSB, [ 10 B 24 H 22 S 2 ] 4− ).
10 B-carrier solution was administered to the tumor-bearing mice subcutaneously into nuchal sites in a volume of 0.02 mL·g −1 per mouse body weight. Doses of 250, 500, or 750 mg·kg −1 of BPA are equal to 12.0, 24.0 and 36.0 mg 10 B·kg −1 . Doses of 125, 250, or 375 mg·kg −1 of BSH are equal to 71.0, 142.0 and 213.0 mg 10 B·kg −1 . At various time points after the administration through subcutaneous injection into nuchal sites, mice were sacrificed and tumors were excised. Additionally, blood samples were collected through heart puncture. The 10 B concentrations in these tissues were measured by prompt γ-ray spectrometry using a thermal neutron guide tube installed at the Kyoto University Reactor (KUR) (Kobayashi and Kanda1983).
Labeling with 5-bromo-2′-deoxyuridine (BrdU)
Nine days after the tumor cell inoculation, mini-osmotic pumps (Durect Corporation, Cupertino, CA, USA) containing BrdU dissolved in physiological saline (200-250 mg·ml−1) were implanted subcutaneously, to label all P cells, for 5 days. Administration of BrdU did not change the tumor growth rate. The tumors were 1 cm in diameter at treatment. The labeling index after continuous labeling with BrdU was 55.3 ± 4.5 (mean ± standard deviation) %, and reached a plateau level at these stages. Therefore, we regarded tumor cells not incorporating BrdU after continuous labeling as Q cells.
Since the intratumor 10 B concentration during neutron irradiation is a crucial determinant for the cell-kill effect in BNCT, irradiation was started at selected time points after the subcutaneous injection of the 10 B-carriers at a selected dose of 10 B. Based on a preliminary study of the biodistribution of 10 B, irradiation was started from 60 min after the subcutaneous injection, and finished by 180 min after the injection.
To irradiate the tumors implanted into the left hind legs of mice, a device made of acrylic resin and capable of holding 12 mice was used, and the tumor-bearing mice were irradiated with a reactor neutron beam at a power of 1 MW at KUR or γ-rays after being fixed in position with adhesive tape. A lithium fluoride (LiF) thermoplastic shield was employed to avoid irradiating other body parts except implanted solid tumors. Neutron irradiation was performed using a reactor neutron beam with a cadmium ratio of 9.4. The neutron fluence was measured from the radioactivation of gold foil at both the front and back of the tumors. Since the tumors were small and located just beneath the surface, the neutron fluence was assumed to decrease linearly from the front to back of the tumors. Thus, we used the average neutron fluence determined from the values measured at the front and back. Contaminating γ-rays, including secondary γ-rays, doses were measured with a thermoluminescence dosimeter (TLD) powder at the back of the tumors. The used TLD was beryllium oxide (BeO) enclosed in a quartz glass capsule. BeO itself has a fairly strong sensitivity to thermal neutrons. The thermal neutron fluence of 8 × 10 12 cm −2 is equal to an approximately 1 cGy γ-ray dose. We usually use the TLD together with gold activation foil for neutron-sensitivity correction. The details were described in the following reference (Sakurai and Kobayashi2000). To estimate neutron energy spectra, eight kinds of activation foil and fourteen kinds of nuclear reaction were used (Sakurai and Kobayashi2000). The absorbed dose was calculated using the flux-to-dose conversion factor (Kobayashi et al.2000). The tumors contained H (10.7 % in terms of weight), C (12.1 %), N (2 %), O (71.4 %), and other elements (3.8 %) (Snyder et al.1975). The average neutron flux and Kerma rate of the employed beams were 1.0 × 109 n·cm −2 ·s −1 and 48.0 cGy·h −1 for the thermal neutron range (less than 0.6 eV), 1.6 × 108 n·cm −2 ·s −1 and 4.6 cGy·h −1 for the epithermal neutron range (0.6 through 10 keV), and 9.4 × 106 n·cm −2 ·s −1 and 32.0 cGy·h −1 for the fast neutron range (more than 10 keV), respectively. The Kerma rate for the boron dose per Φ n·cm −2 ·s −1 of thermal neutron flux for 1 μg·g −1 of 10 B was 2.67 × 10 −8 Φ cGy·h −1 . The dose rate of γ-rays including contaminating γ-rays in reactor neutron beams and γ-rays resulting from capture of thermal neutrons by hydrogen atoms [ 1 H(n,γ) 2 H] was 66.0 cGy·h −1 . Irradiation with γ-rays was performed with a cobalt-60 γ-ray irradiator at a dose rate of approximately 2.0 Gy·min −1 .
Each irradiation group also included mice that were not pretreated with BrdU.
Immunofluorescence staining of BrdU-labeled cells and micronucleus assay
Right after the in vivo irradiation of the implanted tumors, tumors were excised from the mice given BrdU, minced, and trypsinized (0.05% trypsin and 0.02% ethylenediamine-tetraacetic acid (EDTA) in phosphate-buffered saline [PBS], 37°C, 15 min). Tumor cell suspensions thus obtained were incubated for 72 h in tissue culture dishes containing complete medium and 1.0 μg·ml−1 of cytochalasin-B to inhibit cytokinesis while allowing nuclear division, and the cultures were then trypsinized and cell suspensions were fixed. After the centrifugation of fixed cell suspensions, each cell pellet was resuspended with cold Carnoy’s fixative (ethanol:acetic acid = 3:1 in volume). The suspension was then placed on a glass microscope slide and the sample was dried at room temperature. The slides were treated with 2M hydrochloric acid for 60 min at room temperature to dissociate the histones and partially denature the DNA. The slides were then immersed in borax-borate buffer (pH 8.5) to neutralize the acid. BrdU-labeled tumor cells were detected by indirect immunofluorescence staining using a monoclonal anti-BrdU antibody (Becton Dickinson, San Jose, CA, USA) and a fluorescein isothiocyanate (FITC)-conjugated antimouse IgG antibody (Sigma, St. Louis, MO, USA). To observe the double staining of tumor cells with green-emitting FITC and red-emitting propidium iodide (PI), cells on the slides were treated with PI (2 μg/ml in PBS) and monitored under a fluorescence microscope.
When cell division is disrupted, or the chromosomes are broken or damaged by chemicals or radiation, then the distribution of genetic material between the two daughter nuclei during cell division is affected and pieces or entire chromosomes fail to be included in either of the two daughter nuclei. The genetic material that is not incorporated into a new nucleus forms its “micronucleus (MN)”. Thus, the frequency of micronucleus formation very well reflects the genotoxicity of a chemical compound and radiation. The MN frequency in cells not labeled with BrdU could be examined by counting the micronuclei in the binuclear cells that showed only red fluorescence. The MN frequency was defined as the ratio of the number of micronuclei in the binuclear cells to the total number of binuclear cells observed. The ratios obtained in tumors not pretreated with BrdU indicated the MN frequency at all phases in the total (P + Q) tumor cell population. More than 400 binuclear cells were counted to determine the MN frequency (Masunaga and Ono2002).
Clonogenic cell survival assay
Surviving fraction and micronucleus frequency at 0 Gy
Total tumor cells
<Plating efficiency (%)>
70.7 ± 8.8 a
BPA b (250 mg/kg)
45.5 ± 5.8
BPA (500 mg/kg)
40.5 ± 4.6
BPA (750 mg/kg)
39.4 ± 3.8
BSH c (125 mg/kg)
54.0 ± 6.8
BSH (250 mg/kg)
50.0 ± 5.8
BSH (325 mg/kg)
44.8 ± 4.8
0.029 ± 0.007
0.053 ± 0.007
BPA (250 mg/kg)
0.045 ± 0.010
0.067 ± 0.008
BPA (500 mg/kg)
0.050 ± 0.011
0.073 ± 0.009
BPA (750 mg/kg)
0.054 ± 0.012
0.078 ± 0.012
BSH (125 mg/kg)
0.042 ± 0.005
0.069 ± 0.011
BSH (250 mg/kg)
0.047 ± 0.005
0.075 ± 0.010
BSH (325 mg/kg)
0.052 ± 0.007
0.081 ± 0.012
Three mice were used to assess each set of conditions and each experiment was repeated twice. To examine the differences between pairs of values, the Student’s t-test was used when variances of the two groups could be assumed to be equal; otherwise, the Welch t-test was used. P-values are from two-sided tests.
Based on the data in Table 1, BPA or BSH treatment induced a significantly lower PE and higher MN frequency in both the Q and total cell populations (P < 0.05) than no drug treatment. Q cells showed significantly higher MN frequencies than the total cell population under each set of conditions (P < 0.05). Further, although not significantly, as the administered doses of 10 B-carriers increased, the changes in the PE and MN frequency tended to become more remarkable compared with no drug treatment.
Based on the findings concerning these 10 B biodistribution patterns, irradiation was started from 60 min and was finished by 180 min after the subcutaneous administration of the 10 B-carriers, because it took approximately 60 through 120 min to deliver a sufficient physical dose of radiation to solid tumors with reactor neutron beams. The 10 B concentrations during irradiation in tumors for BPA administration at the doses of 250, 500 and 750 mg·kg −1 were 17.5 ± 1.7 μg·g −1 , 22.5 ± 6.9 μg·g −1 and 25.0 ± 5.2 μg·g −1 , respectively. The 10 B concentrations during irradiation in tumors for BSH administration at the doses of 125, 250 and 375 mg·kg −1 were 17.3 ± 1.7 μg·g −1 , 22.2 ± 6.9 μg·g −1 and 25.7 ± 5.0 μg·g −1 , respectively.
When neutron beams were employed, radiation dose means the physical radiation dose due to energy deposition from 3 types of radiation: (a) low LET γ-rays resulting from capture of thermal neutrons by hydrogen atoms [ 1 H(n,γ) 2 H], and from the contaminating external γ-rays originally included in the employed neutron beams; (b) high LET protons produced by the scattering of fast neutrons and from capture of thermal neutrons by nitrogen atoms [ 14 N(n,p) 14 C]; and (c) high LET, heavier-charged α particles and 7 Li ions released as products of the thermal neutron capture and fission reactions with 10 B [ 10 B(n,α) 7 Li] in the presence of 10 B.
The data on cell survival following γ-ray irradiation only were fitted to the linear quadratic (LQ) dose relationship (Hall2012). The clonogenic cell survival curves after in vivo irradiation using reactor neutron beams following administration of the 10 B-carrier were obtained as the cell survival curves for “neutron beams”. When reactor neutron beams were employed for irradiation, the data on cell survival following reactor neutron beam irradiation were normalized with the data on cell survival for γ-ray irradiation only by dividing the data for neutron beams by the data for γ-ray irradiation only in order to obtain the data on cell survival for irradiation with “neutrons only” (Hopewell et al.2012; Hall2012). At this normalization, the dose reduction factor for γ-rays of 0.45 was taken into consideration because the γ-ray dose rate of employed neutron beams was much less than 1 Gy·min −1 , that is, 0.011 Gy·min −1 (Hopewell et al.2011; Hopewell et al.2012). Similarly, the data on cell survival for irradiation with “neutrons only” without administration of the 10 B-carrier were fitted to the LQ dose relationship. Further, when reactor neutron beams were employed for irradiation following administration of the 10 B-carrier, the data on cell survival for irradiation with “neutrons only” with the administration of the 10 B-carrier were normalized with the data on cell survival for irradiation with “neutrons only” without the administration of the 10 B-carrier by dividing the data for “neutrons only” with the 10 B-carrier by the data for irradiation with “neutrons only” without the 10 B-carrier in order to obtain data on cell survival for irradiation at the “ 10 B dose”.
When the 10 B-carrier was employed, even if no radiation was given, MN frequencies were higher than when no 10 B-carrier was administered because of the slight genotoxicity of the drug (Table 1). Therefore, for background correction, we used the net MN frequency to exclude the effects of the genotoxicity of the 10 B-carrier. The net frequency is the frequency in the irradiated tumors minus the frequency in the nonirradiated tumors.
The data on net MN frequency following γ-ray irradiation only were also fitted to the linear quadratic (LQ) dose relationship (Hall2012). The dose-response curves of the net MN frequency after in vivo irradiation using reactor neutron beams following administration of the 10 B-carrier were obtained as the dose-response curves of net MN frequencies for “neutron beams”. When reactor neutron beams were employed for irradiation, the data on the net MN frequency following reactor neutron beam irradiation were normalized with the data on the net MN frequency for γ-ray irradiation only by subtracting the data for γ-ray irradiation only from the data for neutron beams in order to obtain the data on the net MN frequency for irradiation with “neutrons only”. At this normalization, the dose reduction factor for γ-rays of 0.45 was also taken into consideration. Similarly, the data on the net MN frequency for irradiation with “neutrons only” without administration of the 10 B-carrier were fitted to the LQ dose relationship. Further, when reactor neutron beams were employed for irradiation following administration of the 10 B-carrier, the data on the net MN frequency for irradiation with “neutrons only” with the administration of the 10 B-carrier were normalized with the data on the net MN frequency for irradiation with “neutrons only” without the administration of the 10 B-carrier by subtracting the data for irradiation with “neutrons only” without the 10 B-carrier from the data for “neutrons only” with the 10 B-carrier in order to obtain data on the net MN frequency for irradiation at the “ 10 B dose” (Hopewell et al.2011; Hopewell et al.2012; Coderre et al.2003).
The values of relative biological effectiveness and compound biological effectiveness factors
Total tumor cells
<Surviving fraction = 0.01>
BPA a (250 mg/kg)
BPA (500 mg/kg)
BPA (750 mg/kg)
BSH b (125 mg/kg)
BSH (250 mg/kg)
BSH (325 mg/kg)
<Net micronucleus frequency = 0.7>
BPA (250 mg/kg)
BPA (500 mg/kg)
BPA (750 mg/kg)
BSH (125 mg/kg)
BSH (250 mg/kg)
BSH (325 mg/kg)
Dose modifying factors a for quiescent tumor cells relative to the total tumor cell populations
<Net micronucleus frequency = 0.7>
1.85 (1.7-2.0) b
BPA c (250 mg/kg)
BPA (500 mg/kg)
BPA (750 mg/kg)
BSH d (125 mg/kg)
BSH (250 mg/kg)
BSH (325 mg/kg)
We administered the 10 B-carrier not intraperitoneally but subcutaneously since high 10 B concentration in tumors was thought to be able to be kept as long as possible compared with intraperitoneal administration. Actually, which 10 B-carrier was employed, the decreasing pattern of 10 B concentration in tumors was not so rapid as intraperitoneal administration (Masunaga et al.2004). The biodistribution patterns in SCC VII tumors as a whole of 10 B from subcutaneously administered BPA at doses of 250, 500 and 750 mg·kg−1 were very similar to those from BSH at doses of 125, 250, and 375 mg·kg−1 , respectively, except at 30 min after administration, when the concentration of 10 B from BSH was much higher than that from BPA. Therefore, the 10 B concentrations during irradiation, which was started from 60 min and finished by 180 min after administration, in tumors for BPA administration at doses of 250, 500 and 750 mg·kg −1 were also very similar to those for BSH administration at doses of 125, 250 and 375 mg·kg −1 , respectively. This is probably because the tumor distribution of 10 B from BSH is mostly dependent on the diffusion of the drug, whereas that from BPA is more dependent on the ability of the tumors to take up 10 B (Masunaga and Ono2002). This is also thought to support the finding that 10 B from BSH in blood, that was higher than that from BPA, washed away more rapidly than that from BPA.
Solid tumors, especially human tumors, are thought to contain a high proportion of Q cells . The presence of Q cells is probably due, in part, to hypoxia and the depletion of nutrients in the tumor core, another consequence of poor vascular supply (Vaupel2004). This may promote the formation of micronuclei at 0 Gy in Q tumor cells (Table 1) and induce a higher level of tumor heterogeneity in Q than P tumor cells (Vaupel2004). Q cells were shown to have significantly less radio-sensitivity than the total cells here (Figure 2). This means that more Q cells survive radiation therapy than P cells. Thus, the control of Q cells has a great impact on the outcome of radiation therapy. The frequency of closely spaced DNA lesions forming a cluster of DNA damage produced by high LET radiation is thought to be much less dependent on oxygenation status at the time of irradiation than that of DNA damage produced by low LET γ-ray irradiation (Hamada et al.2010). Accordingly, in both the total and Q cell populations, neutron only irradiation was less dependent on oxygenation status, leading to much higher RBE values compared with γ-ray irradiation in Q than the total tumor cell population (Table 2) (Hamada et al.2010). In terms of the tumor cell-killing effect as a whole, including intratumor Q cell control, neutron only beam radiotherapy is a promising treatment for refractory tumors.
Actually, BNCT is a mixed field irradiation. The principal dose components, in addition to the α-particles and 7 Li ions resulting from the boron capture reaction: 10 B + 1 n = 7 Li + 4 He(α) + 2.79 MeV include γ-rays (dγ), both incident within the neutron beam and induced by the neutron capture reaction in hydrogen: 1 H + 1 n = 2 H + γ + 2.2 MeV plus protons, either as recoil protons (d n ) from fast neutron interactions, largely with hydrogen, or from neutron capture (d N ) by nitrogen in tissue: 14 N + 1 n = 14 C + 1 p + 580 keV. These various absorbed dose components, contributing to the total radiation dose, are usually assumed to act independently of each other. Thus the total photon-equivalent dose(D w ) is given by the following equation: D w = (dγ × DRF) + (d n × RBE n ) + (d N × RBE N ) + ( 10 B × CBE) where DRF is the dose reduction factor for γ-rays, which varies with dose rate; RBE n is the relative RBE of fast neutrons, which depends on neutron energy, RBE N the equivalent value for protons from the nitrogen capture reaction and CBE, which is derived from two factors: the RBE of α-particles and 7 Li ions and the microdistribution of 10 B in a particular tissue. Due to the short range of these particles in tissue, 9 and 5 μm, respectively, the biological effect depends critically on both the gross and microscopic distributions of 10 B in tissues (Hopewell et al.2011; Hopewell et al.2012; Coderre et al.2003).
As Q cell populations have been shown to have a much larger hypoxic fraction (HF) than total cell populations (Masunaga and Ono2002), and hypoxic cells are thought to exhibit less uptake than aerobic cells (Masunaga and Ono2002; Masunaga et al.2012), it follows that Q cells have a lower uptake capacity than the total cell population, that is, the distribution of 10 B from 10 B-carriers into Q cells is less dependent on the uptake ability of the cells than on the diffusion of the drugs. Further, taking into consideration that the cellular distribution of 10 B from BSH is more dependent on the diffusion of the drug, whereas that from BPA is more dependent on the ability of the cells to take up 10 B, it was reasonable that the values of CBE factors for BPA were higher than those for BSH in the total tumor population, while in the Q cell population, those for BPA were lower than those for BSH. Consequently, as shown before (Ono et al.1999; Masunaga and Ono2002), when 10 B-carrier is employed for the selective tumor cell-killing effect as a whole, the combined use with BPA and BSH can be one of the promising techniques in BNCT.
Meanwhile, the increase in the 10 B concentrations in tumors did not keep pace with that in the concentrations of the administered 10 B-carriers. In other words, the values of CBE factors showed a decreasing tendency as the concentrations of the administered 10 B-carriers increased, especially in the Q tumor cell population when BPA was employed. These were thought to be partially due to the tumor heterogeneity. Especially, the decrease in the values of CBE factors showed the difficulty in the homogeneous distribution of 10 B throughout solid tumors, particularly in the Q cell population, partially due to the degree of the tumor heterogeneity. Thus, this may mean that the values of CBE factors can reflect the level of tumor heterogeneity of solid tumors (Hopewell et al.2012; Hall2012).
In BNCT, compared with reactor neutron beam irradiation only, Q cells have been shown to have significantly less radio-sensitivity than the total cell population when a 10 B-carrier, especially BPA, is employed (Table 3) (Masunaga and Ono2002; Masunaga et al.2012). Thus, more Q cells can survive BNCT than P cells. In addition, when a 10 B-carrier was used, this difference in the radio-sensitivity between total and Q cell populations increased as the concentrations of administered 10 B-carriers increased. This was also partially because the increase in distributing 10 B from a 10 B-carrier into the Q cell population did not keep pace with that in the concentrations of the administered 10 B-carriers. In other words, intratumor microenvironmental heterogeneity has a greater impact on the 10 B concentration in solid tumors as a higher concentration of a 10 B-carrier is administered. This also means that a newly developed 10 B-containing drug not only should be non-toxic to normal cells but 10 B from the drug also has to be delivered as homogenously as possible throughout the tumors over the intratumor heterogeneity.
Tumor heterogeneity is now thought to be one of the major difficulties in the treatment of solid tumors (Marusyk et al.2012; Bhatia et al.2012). Many tumors contain phenotypically and functionally heterogeneous cancer cells. The most well-established mechanism involves intrinsic differences among cancer cells caused by stochastic genetic or epigenetic changes (clonal evolution). Differences can also arise among cancer cells through extrinsic mechanisms in which different microenvironments within a tumor confer phenotypic and functional differences upon cancer cells in different locations (Magee et al.2012). It is well known that tumor vessels are characteristically dilated, saccular and tortuous and exhibit large inter-endothelial cell junctions, increased numbers of fenestrations and lack of normal basement membrane. The abnormal structure of tumor blood vessels compromise blood flow and hinder effective convective fluid transport, resulting in the impaired distribution of blood-borne therapeutic agents (Vaupel2004). Thus, increasing the dose of 10 B compound might not be effective however much drug is administered. Finally, some cancers follow a stem cell model in which tumorigenic cancer stem cells “differentiate” into nontumorigenic cancer cells, creating a hierarchical organization (Bhatia et al.2012). The differentiation of cancer stem cells provides a mechanism for generating phenotypic and functional heterogeneity beyond the heterogeneity that can be attributed to clonal evolution or environmental differences (Magee et al.2012). Meanwhile, when the clinical outcome of the Argentine cutaneous melanoma treatments was assessed with regard to the doses derived from the standard procedure, the use of fixed RBE values was shown to have a formal inconsistency, which in practice lead to unrealistically high tumor doses, and it was reported that the fixed RBE approach was not suitable to understand the observed clinical results in terms of the photon radiotherapy data (Gonzalez and Santa Cruz2012).
The CBE factor for each tissue and tumor, which was shown to greatly depend on the degree of the possibility for distributing 10 B from a 10 B-carrier, may be one of promising candidates for the index for estimating tumor heterogeneity. In the future, we would like to analyze the CBE factor in details not only as a parameter in BNCT, but also as a significant index for assessing intratumor heterogeneity.
This study was supported in part by a Grant-in-aid for Scientific Research (B) (23300348) from the Japan Society for the Promotion of Science.
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