Method for treatment of central nervous system tumors

Abstract

To provide a method for treating central nervous system tumors such as gliomas.SOLUTION: The method comprises delivering a β-emitting radionuclide-containing composition to a tumor via the cerebral vasculature.SELECTED DRAWING: None

Description

[Technical Field]

[0001] The present invention relates to the treatment of central nervous system (CNS) tumors using beta-emitting radionuclides (β-ray-emitting radionuclides), particularly when delivered via the cerebral vasculature. In particular, the present invention relates to the use of injectable compositions comprising radionuclide-containing materials in the treatment of CNS tumors, more particularly high-grade axial brain tumors, including hypervascular tumors such as gliomas. [Background technology]

[0002] Central nervous system (CNS) cancers can be very difficult to treat, with high-grade gliomas being difficult to remove surgically and often resistant to radiation and chemotherapy. Glioblastoma multiforme (GBM) is the most common and most aggressive malignant cancer of the central nervous system. Summary of the Invention [Problem to be solved by the invention]

[0003] The current standard of care is external beam radiation therapy (EBRT) combined with chemotherapy, which has relatively poor outcomes. [Means for solving the problem]

[0004] The present invention relates to the treatment of central nervous system (CNS) tumors using beta-emitting radionuclides (β-ray-emitting radionuclides), particularly when delivered via the cerebral vasculature. In various aspects, the present disclosure provides methods of treating a patient in need of treatment for a CNS tumor, comprising selectively administering a beta-radiation-emitting composition to the cerebral vasculature. In some embodiments, the CNS tumor can be a glioma. In some embodiments, the CNS tumor can be an intraaxial brain tumor. In some embodiments, the CNS tumor can be a meningioma. In some embodiments, the CNS tumor can be a brain metastasis.

[0005] In some embodiments that can be used in conjunction with any of the above aspects and embodiments, the β-radiation-emitting composition is further localized in the T2 hyperintense area of ​​the brain.In this respect, localization in the T2 hyperintense area surrounding the tumor is in addition to targeting the tumor itself.This additional coverage can be advantageous, for example, when the tumor extends to the T2 hyperintense area but does not appear on imaging.

[0006] In some embodiments that can be used in combination with any of the above aspects and embodiments, the beta-emitting composition comprises: 3 H, 14 C. 32 P, 59 Fe, 47 Ca, 89 Sr, 90 Y, 131 I, 153 Sm, 177 Lu7, 166 Ho, and 169 The radionuclides include one or more radionuclides selected from Er.

[0007] In some embodiments that can be used in combination with any of the above aspects and embodiments, the beta-emitting composition can comprise particles having an average diameter of 1-100 μm and including a beta-emitting radionuclide, among others. In particular embodiments, the particles are oil, glass, or polymer particles including a beta-emitting radionuclide and having an average diameter of 1-100 μm. In some of these embodiments, the average diameter is 10-50 μm, more particularly 15-35 μm. In some of these embodiments, the diameter of the particles is 15-35 μm, more particularly 20-30 μm.

[0008] In some embodiments that can be used in combination with any of the above aspects and embodiments, the beta-ray emitting particles are 3 H, 14 C. 32 P, 59 Fe, 47 Ca, 89 Sr, 90 Y, 131 I, 153Sm, 177 Lu7, 166 Ho, and 169 The radionuclides include one or more radionuclides selected from Er.

[0009] In some embodiments that can be used in combination with any of the above aspects and embodiments, the beta-ray emitting particles are glass particles or polymer particles. In some embodiments that can be used in conjunction with any of the above aspects and embodiments, the beta-ray-emitting particles are alumina silicate glass particles containing yttrium, e.g., the glass particles can be formed from a glass obtained from a mixture of 35-45% Y2O3, 15-25% Al2O3, and 35-45% SiO2, such as glass particles formed from a glass obtained from a mixture of about 40% Y2O3, about 20% Al2O3, and about 40% SiO2. In some cases, at least a portion of the yttrium in the glass can be converted to yttrium by exposure to radiation. 90 is converted to Y.

[0010] In some embodiments, which can be used in combination with any of the above aspects and embodiments, the particles are pure beta-emitting particles that emit substantially 100% beta radiation. In some embodiments that can be used in combination with any of the above aspects and embodiments, the particles have a specific activity in the range of 0.05 to 0.005 GBq / mg when administered, and more particularly, a specific activity in the range of 0.0231 to 0.03894 GBq / mg when administered.

[0011] In another aspect, the present disclosure provides an injectable composition containing a suspension of a beta-emitting material in an aqueous liquid for use in treating CNS tumors. In some embodiments, the material is 3 H, 14 C. 32 P, 59 Fe, 47 Ca, 89 Sr, 90 Y, 131 I, 153 Sm, 177 Lu7,166 Ho, and 169 The radionuclides include one or more radionuclides selected from Er.

[0012] In some embodiments, the substance may include particles, such as oil, glass, or polymer particles, having an average diameter of, for example, 1 to 100 μm, among other possible values. In some embodiments, the particles are 3 H, 14 C. 32 P, 59 Fe, 47 Ca, 89 Sr, 90 Y, 131 I, 153 Sm, 177 Lu7, 166 Ho, and 169 The beta-ray emitting particles contain one or more radionuclides selected from Er.

[0013] In some embodiments, the particles are Yttrium 90 ( 90 The beta-emitting particles include insoluble glass microspheres having a diameter (Y) in the range of 20-30 μm, for example, among other possible values. In certain embodiments, each milligram of glass microspheres may contain 22,000-73,000 microspheres. In some embodiments that can be used in combination with any of the above aspects and embodiments, the beta-emitting particles are provided in sterile, pyrogen-free water.

[0014] Additional aspects and embodiments will become apparent to those skilled in the art upon review of the following detailed description. [Brief explanation of the drawings]

[0015] [Figure 1] Angiogram showing contrast agent injected into the left middle cerebral artery of a healthy subject dog. [Figure 2]A) Pre-treatment MRI image and B) Post-treatment Y90 PET / CT fused with pre-treatment MRI. The fused image shows the correlation between MRI T2-enhanced periphery and Y90 PET deposition in the first treated dog with brain tumor. [Figure 3] A) T2 FLAIR MRI image 1 month before treatment, B) T2 FLAIR MRI image 1 month after treatment, C) T1 contrast-enhanced MRI image 1 month before treatment, and D) T1 contrast-enhanced MRI image 1 month after treatment. One month after treatment, there is resolution of perilesional edema, no contrast enhancement, and a decrease in lesion size. There is also resolution of midline shift without evidence of cortical atrophy. DETAILED DESCRIPTION OF THE INVENTION

[0016] As noted above, the present invention relates to the treatment of central nervous system (CNS) tumors using beta-emitting radionuclides (β-ray-emitting radionuclides), particularly when delivered via the cerebral vasculature. In particular, the present invention relates to the use of injectable compositions comprising radionuclide-containing materials in the treatment of CNS tumors, more particularly high-grade axial brain tumors, including hypervascular tumors such as gliomas.

[0017] In preferred embodiments, the present disclosure also relates to the use of injectable compositions comprising radionuclide-containing materials in the treatment of CNS tumors, and more particularly, (1) intraaxial brain tumors (including, but not limited to, primary axial brain tumors), including astrocytomas, primary CNS lymphomas, glioblastomas, and gliomas (such as gliomas or oligodendrogliomas), (2) extraaxial tumors such as meningiomas, and (3) secondary brain tumors arising elsewhere in the body (i.e., brain metastases).

[0018] CNS cancers can be extremely challenging to treat, with high-grade gliomas being difficult to surgically remove and often resistant to radiation and chemotherapy. Glioblastoma multiforme (GBM) is the most common and most aggressive malignant cancer of the central nervous system. The current standard of care is external-beam radiation therapy (EBRT) combined with chemotherapy, with relatively poor outcomes. Researchers at the Johns Hopkins Comprehensive Brain Tumor Center have developed the GliaSite™ Radiation Therapy System (RTS), which delivers radiation from within the cavity created by the surgical removal of malignant brain tumors. Internal radiation "brachytherapy," using manually inserted encapsulated gamma emitters, is an established treatment for cancers of tissues such as the prostate and is being trialed for GBM.

[0019] GBM is a hypervascular tumor that always has an invasive tumor component. This precludes cure by surgery in virtually all cases, making GBM extremely difficult to treat. Poor surgical outcomes also distinguish GBM from solid abdominal tumors (HCC, RCC) in that surgical resection has a very limited role. After considering surgical treatment options for GBM, the standard of care is fractionated external beam radiation therapy (EBRT).

[0020] EBRT typically consists of 35 daily fractions of 1.8 Gy, delivering a total of 63 Gy, including a 1-2 cm margin from the tumor and enhancing margin. Radiation therapy has been used to treat GBM since the 1940s, and preliminary radiobiological thresholds identified in the 1970s indicate a modest 2.3-fold increase in survival at 60 Gy. Modern EBRT treatments using stereotactic techniques and dose-escalation protocols have not reproducibly improved survival (Gzell, C., Back, M., Wheeler, H., Bailey, D. & Foote, M. Radiotherapy in Glioblastoma: the Past, the Present and the Future. Clinical Oncology 29, 15-25 (2017)). However, the combination of EBRT and chemotherapy (e.g., temozolomide, alkylating agents) has been the standard of care since 2002, following data from Stupp et al. demonstrating a median survival of 16 months (see Stupp, R. et al. Promising survival for patients with newly diagnosed glioblastoma multiforme treated with concomitant radiation plus temozolomide followed by adjuvant temozolomide. J. Clin. Oncol. 20, 1375-1382 (2002)).

[0021] Apart from EBRT, manual low-dose-rate brachytherapy has been explored for the treatment of GBM. 125I and more recently 131Cs brachytherapy have been used in combination with standard external beam radiation therapy for salvage after recurrence. For newly diagnosed GBM, overall survival of up to 28.5 months has been reported in several series (see Neurosurgical review (2016). doi:10.1007 / s10143-016-0727-6 and Schwartz, C. et al. Outcome and toxicity profile of salvage low-dose-rate iodine-125 stereotactic brachytherapy in recurrent high-grade gliomas. Acta neurochirurgica 157, 1757-64 discussion 1764 (2015)).

[0022] However, both EBRT and manual brachytherapy using low-energy gamma emitters are associated with high radiation doses to healthy brain parenchyma, resulting in a high incidence of neurotoxicity. To counter neurotoxicity, advanced techniques such as proton or X-ray microchannels, which use microbeam fields to irradiate tumors, have shown promise for sparing non-cancer parenchyma (see Girst, S. et al. Improved normal tissue protection by proton and X-ray microchannels compared to homogeneous field irradiation. Phys Med 31, 615-620 (2015)).

[0023] High-grade gliomas, by definition, are characterized by hypervascular MR enhancement, which distinguishes low-grade (WHO I, II) from high-grade gliomas (WHO III, IV). Numerous angiogenic factors have been found in association with the various classifications of high-grade gliomas (see Hanif, F., Muzaffar, K., Perveen, K., Malhi, SM & Simjee, SU Glioblastoma Multiforme: A Review of its Epidemiology and Pathogenesis through Clinical Presentation and Treatment. Asian Pacific journal of cancer prevention: APJCP 18, 3-9 (2017)).

[0024] GBM typically presents as a hypercellular, enhancing mass. In fact, contrast enhancement on CT can be over 20 times greater in tumors compared with normal paracetamol (Figure 1). A challenging aspect of GBM therapy is the relatively hypocellular, invasive disease that is always present. While the invasive component poses therapeutic challenges, recurrences after EBRT typically occur centrally within 1–2 cm of the original tumor margins.

[0025] GBM has a well-described dose-response relationship with radiation therapy. Brachytherapy, which involves placing sealed radioactive sources into the tumor, has shown efficacy in some reports, but heterogeneous overall survival rates reflect rates of neurotoxicity approaching 50%. The high neurotoxicity of manual brachytherapy may be due to the wide dose margins resulting from the use of low-energy gamma emitters. This toxicity can be partially mitigated with stereotactic EBRT by avoiding critical neurological structures. See Corwin, D. et al. Toward Patient-Specific, Biologically Optimized Radiation Therapy Plans for the Treatment of Glioblastoma. PLoS ONE 8, e79115 (2013).

[0026] The present inventors hypothesized that transarterial radioembolization (TARE), an established treatment for liver tumors, may be a potentially viable improved treatment for central nervous system cancers in the brain. GBM has a well-described dose-response relationship with radiation therapy. While the brain lacks a dual blood supply like the liver, GBM is by definition hypervascular (10:1 contrast enhancement is possible with GBM). This limits the concentration of arterially administered substances in normal brain parenchyma. Modern EBRT specifically targets hypervascular areas with high doses to improve response, and has achieved some success. Therefore, TARE may offer a similar benefit.

[0027] Manual brachytherapy using low-energy gamma emitters (I, Cs), known as GBM, is associated with high neurotoxicity in nearby neural structures due to the high dose. To mitigate such effects, the inventors hypothesized that radiation emitted from radionuclides placed in the cancer vasculature with a limited range of action would limit the dose and damage to normal tissue. In particular, they determined that beta-emitting radionuclides, especially in a form suitable for TARE, may have the correct profile for limiting the dose to nearby normal tissue.

[0028] Superselective angiography of GBM was described nearly 20 years ago and has been reported many times since then. See Tomura, N. et al. Superselective angio-CT of brain tumors. AJNR Am J Neuroradiol 17, 1073-1080 (1996). Superselective intra-arterial cerebral infusion (SIACI) has been used with some success when delivering drug combinations (see Riina HA, Knopman J, Greenfield JP, et al. Balloon-assisted superselective intra-arterial cerebral infusion of bevacizumab for malignant brainstem glioma. A technical note. Interventional Neuroradiology. 2010;16:71-76).

[0029] The inventors have developed a method for treating a pulmonary artery disease using manual brachytherapy. 125 I, 131 It was hypothesized that the dose deposition margin of beta rays is much narrower compared to that from gamma ray emitters such as Cs, and therefore may not harm soft tissues not involved in cancer. 90 Y is the most energetic pure beta emitter commonly used in radionuclide therapy. 131 I and 177 Lu et al. 90 Alternatives to Y have low-energy beta emissions and may not harm the tissue surrounding ring-enhancing GBM, but the low margins may also result in ineffective treatment of the cellular and / or acellular invasive tumor components that are often present. Thus, while the inventors consider the use of any beta-emitting radionuclide to be within the scope of the present disclosure, they particularly favor materials containing high-energy radionuclides, especially 90 Y and 166 It is envisioned that substances used in TARE, such as Ho, will be used.

[0030] In recent years, tailored EBRT algorithms have shown promise. This technique is premised on delivering a higher dose to enhancing tumor components, assuming that areas with the highest vascularity represent areas of high cellularity. A lower dose is delivered to areas of T2 / FLAIR hyperintensity, assuming this reflects infiltrating tumor or hypocellular edema. Tailored EBRT protocols treat enhancing regions with a higher dose (100–130 Gy) to improve response without the significant increase in absorbed dose to normal parenchyma associated with high-dose treatment of the entire tumor mass. The inventors have 90 It was hypothesized that higher energy beta radiation emitters, such as those from Y radionuclides, might match or improve upon this. 90 Y has been shown to deliver a large absorbed dose (~1000 Gy) to the highly vascular peritumoral area in post-treatment biopsy specimens of liver cancer, potentially improving EBRT in this respect.

[0031] Other techniques of EBRT, such as X-rays and proton microchannels, which avoid harming the brain parenchyma not involved in cancer, are glass 90 Comparison of Y microspheres with EBRT has shown reduced neurotoxicity, similar to the difference in toxicity in liver treatment (which can be 3-5 fold). 90 A sparse distribution of Y-microspheres may spare this tissue and may function mechanically similarly to the x-ray and proton microchannels that are currently the subject of significant research in EBRT.

[0032] Particularly suitable compositions for use in the methods of the present disclosure include radionuclide-containing materials that are minimally embolic in form, such as oil, polymer, or glass microspheres, and minimally embolic beta-emitting radionuclide containing particles are 3 H, 14 C. 32 P, 59 Fe, 47 Ca, 89 Sr, 90 Y, 131 I, 153 Sm,177 Lu7, 166 Ho, 169 More preferably, the radionuclide may be selected from Er. 89 Sr, 166 Ho, 153 Sm, 177 Lu, 169 Er and 90 Y. Optimally, the beta emitter is in the form of a glass or polymer microsphere. 90 Y radionuclide. In some cases, iodinated radionuclides such as Lipiodol are used. 131 I oil can also be used.

[0033] In one embodiment, a non-radioactive nuclide can be administered into microspheres for delivery to the tumor, and then the non-radioactive nuclide can be activated in situ to convert the nuclide to a radioactive nuclide. In a preferred embodiment, activation is performed using an electron beam. In a more preferred embodiment, activation is performed by directing an electron beam at the perfused target volume or treatment site.

[0034] In one embodiment, the radionuclide can be irradiated externally (i.e., irradiated in situ) instead of being irradiated prior to delivery. In a preferred embodiment, in situ irradiation can be performed using an electron beam. In a more preferred embodiment, irradiation is performed by directing an electron beam at the perfused target volume or treatment site.

[0035] Delivery of beta-emitting materials in superselective ways, such as with oils or microspheres that provide minimal embolization, should be technically feasible for CNS tumors of the brain, such as GBM, especially because there is little variation in cerebral vascular supply and perfusion compared to the conventionally treated hepatic vascular anatomy. Superselective delivery also has the advantage of further limiting the absorbed dose to normal brain parenchyma. See Tomura, N. et al. Superselective angio-CT of brain tumors. AJNR Am J Neuroradiol 17, 1073-1080 (1996).

[0036] TheraSphere (registered trademark, also called TheraSphere or Terasphere) available from Biocompatibles UK Limited is a yttrium 90 ( 90 The glass is composed of insoluble glass microspheres in which yttrium (Y) is an essential component of the glass. The glass is an aluminosilicate glass containing yttrium, obtained from a mixture of 35-45% Y2O3, 15-25% Al2O3, and 35-45% SiO2, more specifically, about 40% Y2O3, about 20% Al2O3, and about 40% SiO2. At least a portion of the yttrium in the glass is destroyed by exposure to radiation. 90 It is converted to Y.

[0037] The average diameter of the spheres ranges from 20 to 30 μm. Each milligram contains 22,000 to 73,000 microspheres. TheraSphere® is supplied in 0.6 mL of pyrogen-free sterile water in a 1.0 mL V-bottom vial secured within a clear acrylic vial shield. TheraSphere® is available in six dose sizes: 3 GBq (81 mCi), 5 GBq (135 mCi), 7 GBq (189 mCi), 10 GBq (270 mCi), 15 GBq (405 mCi), and 20 GBq (540 mCi). Custom dose sizes are also available.

[0038] In one embodiment, smaller dose sizes are used, or a fraction of the above dose sizes are used. In a preferred embodiment, administration may use 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, or 95% of any of the above dose sizes. In a more preferred embodiment, administration uses 5%, 10%, 15%, 20%, 25%, or 30% of any of the above dose sizes. In an optimal embodiment, administration uses 5% or 10% of any of the above dose sizes.

[0039] TheraSphere® has a shelf life of 12 days. In one embodiment, reference is made to the specific activity of the composition at the time of calibration. In one embodiment, the day of calibration is referred to as day 0, days 1 through 7 following the calibration date are referred to as week 1, and days 8 through 12 are referred to as week 2. In one embodiment, calibration refers to day 0 at time zero. In one embodiment, time zero on day 0 is noon EST.

[0040] In a preferred embodiment, the preferred treatment window is from Wednesday of the first week (also referred to as Wednesday 1) to Tuesday of the second week (also referred to as Tuesday of the second week). In a more preferred embodiment, the preferred treatment window is from Thursday 1 to Friday 1.

[0041] A pre-assembled, disposable TheraSphere® administration set is provided with each dose. A TheraSphere® administration accessory kit is provided to new user sites. The kit includes reusable accessories such as an acrylic box base, top shield, removable side shields, bag hooks, and a RADOS RAD-60R radiation dosimeter (or equivalent).

[0042] The pure emitter, yttrium-90, decays to stable zirconium-90 with a physical half-life of 64.1 hours (2.67 days). The mean energy of beta radiation from yttrium-90 is 0.9367 MeV. Following embolization of the yttrium-90 glass microspheres in tumor tissue, the emitted beta radiation provides a therapeutic effect. As with other radionuclide-containing materials for use in the methods of the present disclosure, once TheraSphere® is administered, it loses its radioactivity over time and cannot be reused.

[0043] Microspheres are delivered to the target via a catheter placed in an artery supplying blood to the tumor. Unable to pass through the vasculature due to capillary blockage in arterioles, the microspheres become trapped in the tumor, exerting a localized radiotherapeutic effect while simultaneously inflicting some damage on surrounding normal tissue. See Campbell, AM, Bailey, IH & Burton, MA. Tumor dosimetry in human liver following hepatic yttrium-90 microsphere therapy. Phys Med Biol 46, 487-498 (2001).

[0044] TheraSphere® is indicated for radiation therapy or as neoadjuvant therapy prior to surgery or transplantation in patients with unresectable hepatocellular carcinoma (HCC) who can have an appropriately positioned hepatic artery catheter placed.

[0045] Other beta emitters include SIR-spheres®, 90 Ion exchange resin beads containing Y radionuclides are included. These beads range in diameter from 20 to 60 μm and are available from Sirtex Medical. SIR-spheres may be envisioned for use in the present disclosure. In one embodiment, SIR-spheres will be modified to increase their specific activity in order to enhance the therapeutic effect they exert during their use. In a preferred embodiment, this increase in specific activity is achieved by the addition of a fluorine-containing compound to the resin. 90 This can be achieved by increasing the Y loading.

[0046] Further beta-emitting materials are 131 Iodinated Lipiodol, the use of which is described by the European Society of Nuclear Medicine monograph, and Lipiodol is available from the Guerbet Group.

[0047] In its broadest aspect, the method of the present disclosure comprises administering a beta-radiation emitter selectively to the vasculature supplying a CNS tumor. In particular, the method comprises administering an injectable pharmaceutical composition, e.g., made of a liquid, polymer, or glass, containing beta-radiation-emitting particles in an aqueous carrier, such as saline or sterile water. In one embodiment, the carrier is any injectable medium. In one embodiment, the carrier is or comprises 5% dextrose in water. In one embodiment, the carrier is or comprises ethanol. In one embodiment, the carrier is or comprises an iodinated contrast agent.

[0048] More preferably, the method involves administering the composition to the vasculature supplying CNS tumors in the brain. 3 H, 14 C. 32 P, 59 Fe, 47 Although other radiations may be produced, as well as radionuclides such as Ca, the inventors 89 Sr, 166 Ho, 153 Sm, 177 Lu7, 169 Er, and 90 Y, optimally, 90 It is envisioned that particles containing Y will provide the most appropriate treatment.

[0049] in glass or polymer 90 Compositions containing Y radionuclides are preferred, most preferably as glass particles, more preferably having an average diameter of 1-100 μm. More preferably, the particles should have an average diameter of 10-50 μm, and even more preferably an average diameter of 15-35 μm, for example 20-30 μm.

[0050] The particles are optimally and conveniently supplied as an aqueous suspension, for example a suspension in sterile water or saline. Particle administration preferably begins with a steroid, e.g., 4 mg / kg (IV or PO) prednisone initially, followed by, e.g., 2 mg / kg PO daily initiated on the day of cerebral artery radioembolization, and may be continued at titrated doses of 2-4 mg / kg thereafter until the clinician feels it is safe to discontinue (based on post-treatment MRI).

[0051] The disclosed method particularly involves placing a catheter in a cerebral artery supplying a cancer, e.g., a tumor, of the central nervous system. If the tumor is located in one of the cerebral hemispheres or a subzone thereof, it is more preferable that the catheter be placed in a specific branch of the cerebral artery supplying the tumor.

[0052] In a preferred embodiment, the method of the present disclosure deploys a catheter through the radial artery. Typically, a guide catheter is advanced over a wire, for example, inserted into the aorta via the femoral artery, and advanced into the carotid artery, such as under fluoroscopy.

[0053] Preferably, angiographic evaluation using contrast, for example iodinated contrast, is performed to identify and access the cerebral arterial branches that primarily supply blood to the tumor. The catheter is preferably a microcatheter; one example of a suitable microcatheter is provided by Stryker, Excersior SL-10 1.7F (0.6 mm diameter). A suitable catheter does not use a balloon to isolate the vasculature during administration of the beta-emitting radionuclide-containing composition. In some situations, a balloon, such as that associated with a balloon catheter, may be preferred by clinicians. However, the inventors believe that this is not necessary if appropriate sized particles containing the composition are used.

[0054] Preferably, the microcatheter is advanced as close as possible to the tumor without causing physical damage to the blood vessels. This allows for as selective placement of the beta-emitting composition as possible, e.g., preferably providing primarily localization and preferably some embolization of the tumor with limited perfusion of normal brain parenchyma. An antivasospastic drug, e.g., nitroprusside (100 mcg), is preferably administered by intra-arterial injection to prevent vasospasm during selective arterial catheterization.

[0055] In one embodiment, prior to treatment, a pretreatment MRI is preferably reviewed to determine tumor volume. A research physicist implements a treatment plan with a preferred expected tumor absorbed dose of 30-200 Gy, preferably 50-200 Gy, more preferably 80-180 Gy, and most preferably 100-150 Gy. This treatment dose is injected into the tumor via a microcatheter. After microsphere injection is complete, the wire, catheter, and sheath are removed. For closure, manual pressure is maintained until hemostasis is achieved or a closure device is utilized.

[0056] In one embodiment, the target therapeutic volume is understood to be the area perfused by the administration. In one embodiment, this target therapeutic volume includes both tumor tissue and normal tissue. In one embodiment, a clinician can use anatomical imaging and / or intra-procedural cone beam computed tomography (CBCT) with contrast enhancement to determine the target therapeutic volume.

[0057] In one embodiment, the research physicist performs a treatment plan with an expected treatment volume dose of 10-1000 Gy, preferably 50-200 Gy, more preferably 80-180 Gy, and most preferably 100-150 Gy. As one skilled in the art will appreciate, the tumor absorbed dose is expected to be higher than the normal tissue absorbed dose. Without being bound by theory, this may be due to the hypervascularity of tumors.

[0058] In one embodiment, the desired dose in Gray (Gy) can be calculated based on the target volume using software similar to TheraSphere™ iDOC™ software, using a treatment window illustrator, or using the MIRD schema. In one embodiment, the desired dose in Gray (Gy) can be calculated based on the target treatment volume using software similar to TheraSphere™ iDOC™ software, using a treatment window illustrator, or using the MIRD schema.

[0059] In one embodiment, the desired absorbed dose in Gray (Gy) can be calculated based on the target therapeutic dose using the MIRD schema. In one embodiment, the desired absorbed dose in Gray (Gy) can be calculated based on the target therapeutic dose using software similar to TheraSphere™ iDOC™ or Therapeutic Window Illustrator software.

[0060] In one embodiment, the desired absolute activity, expressed in becquerels (Bq) or gigabecquerels (GBq), can be calculated based on the target therapeutic dose using the MIRD schema. In one embodiment, the desired absolute activity (Bq or GBq) can be calculated based on the target therapeutic dose using software similar to TheraSphereiDOC™ or Therapeutic Window Illustrator software. After closure and hemostasis are achieved, the subject is preferably transferred to the PET / CT scanner for scanning. Anesthesia is maintained, for example, with an IV bolus of propofol. The PET-CT scan is performed under general anesthesia with isoflurane while using a ventilator. The PET / CT scan detects radioactive emissions from administered particles and does not require additional injections of radioactive material. In one embodiment, the scan can be performed without anesthesia.

[0061] After PET / CT, subjects are extubated when the swallowing reflex returns. Potential postoperative pain is managed by subcutaneous / intramuscular injection of analgesics, such as buprenorphine (0.005–0.02 mg / kg q 8–12 h). Subjects may be allowed to return home after a radiation safety study when awake and normothermic. After treatment and imaging, subjects can be discharged the same day. Clinicians should look for behavioral changes or signs of seizures during follow-up. Depending on the severity of these issues, a clinical determination of the possibility of herniation is made based on the subject's behavior, the presence of seizures, cranial nerve deficits, and physical appearance. The investigator may recommend treatment to reduce intracranial pressure.

[0062] Subjects typically undergo post-treatment MRI imaging under anesthesia to assess for signs of inflammation, edema, and other neurological changes, preferably no more than once a week for up to one week after treatment. Sedation and anesthesia will be similar to that described above for cerebral artery radioembolization. In one embodiment, imaging can be performed without anesthesia.

[0063] (Example) The present disclosure is described by reference to the following non-limiting illustrative examples, in light of which further embodiments will occur to those skilled in the art.

[0064] Experimental rationale: There are no suitable large-scale research animal models for glioblastoma multiforme (GMB) that exhibit characteristics characteristic of human brain tumors. These tumors occur naturally in humans but are also commonly found in some canine breeds. Canine cancer models with spontaneously occurring high-grade axial brain tumors, including GBM, are clinically relevant to human cancer and exhibit typical histopathological features, such as pseudonecrosis, angiogenesis, endothelial proliferation, and inflammatory cell infiltration. 10. Schiffman JD, Breen M: Comparative oncology: what dogs and other species can teach us about humans with cancer. Philos Trans R Soc Lond B Biol Sci 2015, 370.

[0065] Advantageously, the use of captive animals with spontaneously arising tumors can minimize the use of research animals while potentially benefiting captive animals. Animals were evaluated for disease before enrollment in the study according to the standard of care at the Johns Hopkins Medicine Center for Image-Guided Animal Therapy, which included (i) a veterinary neurological examination, (ii) blood tests (CBC, chemistry panel), and MRI with contrast.

[0066] Participation in this study involves reviewing an MRI and 90 This relied on identifying tumor characteristics suitable for Y therapy, including tumors that were primarily perfused by one vascular territory and did not involve both hemispheres.

[0067] Research dogs were recruited as safety controls, and captive dogs presenting to the clinic with spontaneous canine gliomas in one hemisphere were used only in the active treatment group.

[0068] result: Treatment in the study dogs proceeded well, with significant absorbed doses delivered to the normal brain. Overall, the study dogs tolerated treatment well.

[0069] The two glioma cases were completed as of the filing date of this patent, and both experiences were similar in terms of procedural imaging impressions. The tumor was treated via the carotid artery, with the goal of covering the half of the brain (right / left) containing the tumor. Some perfusion crossed the midline, resulting in a little over half. The angiogram was unremarkable. While one would expect to see hypervascularity or blushing of the tumor, the tumor was not easily identifiable. 90 Post-Y PET showed good uptake in T2 hyperintense (flare image) areas of the brain surrounding the tumor and in the tumor itself. It was surprising to achieve so much localization in this tumor region of the brain based on the angiogram.

[0070] In the following example, the TheraSphere® is calibrated to noon EST on Sunday, which is designated as day 0. In the following example, the TheraSphere® was calibrated to have a specific activity of 0.11 GBq (±10%) at the time of calibration.

[0071] The first test dog was examined on Thursday of the second week. 90 One dog was treated with TheraSphere® (low-dose radiation - 2 weeks after birth) and experienced a transient ischemic attack after treatment. The second dog was treated with approximately twice as much activity and approximately twice as few microspheres at the Friday dose of week 1. The dog with higher activity and fewer beads did not experience a significant transient ischemic attack after treatment. Higher specific activity microspheres may limit embolic / ischemic effects in the brain. In this regard, embolization of the cerebral vasculature is generally considered negative because it can cause a transient ischemic attack or stroke. The risk of adverse effects from embolization needs to be mitigated by using smaller and fewer microspheres while delivering therapeutic levels of radiation. This can be achieved by using small, high specific activity (activity per gram) microspheres.

[0072] 90By the time of post-Y PET, the first dog's tumor dose was 35 Gy and normal tissue 18.6 Gy. The limited spatial resolution of PET may have resulted in higher tumor doses. The second dog's tumor dose was 115 Gy and normal tissue 23.5 Gy. This separation of tumor and normal tissue in Dog 2 was excellent and may be far superior to what can typically be achieved with external beam radiation. The target tumor dose with external beam radiation is approximately 60 Gy. The short penetration of beta radiation and the relatively large tumor-to-normal ratio should avoid high absorbed doses to normal tissue. Dog 1 showed a complete response approximately 1 month after treatment. Dog 2 has been symptom-free for 11 days.

Claims

1. An injectable composition comprising a suspension of beta-emitting minimally embolic glass particles in an aqueous liquid for use in treating CNS tumors by selectively administering an effective amount of the particles to the cerebral vasculature, wherein the beta-emitting composition is administered at an expected tumor absorbed dose of 30 to 200 Gy, the particles have an average diameter of 10 to 50 μm, the particles contain 22,000 to 73,000 microspheres per milligram, and the particles have a specific activity in the range of 0.05 to 0.005 GBq / mg.

2. The injectable composition of claim 1, wherein the particles comprise one or more radionuclides selected from 3H, 14C, 32P, 59Fe, 47Ca, 89Sr, 90Y, 131I, 153Sm, 177Lu7, 166Ho, and 169Er.

3. The injectable composition of claim 1, wherein the particles are beta-ray emitting particles containing one or more radionuclides selected from 3H, 14C, 32P, 59Fe, 47Ca, 89Sr, 90Y, 131I, 153Sm, 177Lu7, 166Ho, and 169Er.

4. The injectable composition of claim 1, wherein the particles are pure beta-ray emitting particles that emit substantially 100% beta rays.

5. The injectable composition of claim 1, wherein the beta-ray-emitting particles comprise a pure beta-ray-emitting radionuclide selected from 89 Sr, 166 Ho, 153 Sm, 177 Lu, 169 Er and 90 Y.

6. The injectable composition of claim 5, wherein the pure beta-emitting radionuclide is 90Y.

7. The injectable composition of claim 1, wherein the glass particles are aluminosilicate glass particles containing yttrium.

8. The injectable composition of claim 1, wherein the glass particles are formed from a glass obtained from a mixture of 35-45% Y 2 O 3 , 15-25% Al 2 O 3 , and 35-45% SiO 2 .

9. The injectable composition of claim 1, wherein the glass particles are formed from a glass obtained from a mixture of about 40% Y 2 O 3 , about 20% Al 2 O 3 , and about 40% SiO 2 .

10. The injectable composition of claim 1, wherein the glass particles comprise insoluble glass microspheres having yttrium-90 ( 90 Y) as an integral component of the glass.

11. The injectable composition of claim 1, wherein the diameter of the glass microspheres is in the range of 20 to 30 μm.

12. The injectable composition of claim 1, wherein the beta-ray emitting particles are provided in sterile, pyrogen-free water.

13. The injectable composition of claim 1, wherein the CNS tumor is a hypervascular tumor.

14. The injectable composition of claim 1, wherein the CNS tumor is a high-grade axial tumor.

15. The injectable composition of claim 1, wherein the CNS tumor is an intraaxial brain tumor.

16. The injectable composition of claim 1, wherein the CNS tumor is a meningioma.

17. The injectable composition of claim 1, wherein the CNS tumor is a brain metastasis.

18. The injectable composition of claim 1, wherein the beta-emitting composition localizes to T2 hyperintense regions of the brain.

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