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ISSN: 2155-9619
Journal of Nuclear Medicine & Radiation Therapy

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Radiolabeled Immunoglobulin Therapy for Patients with Solid Tumors

Nabil Khater1,2*, Marcel Kap3, Rima Sayah2, Dimor Elbers4 and Huib M Vriesendorp1

1Phase 2 Therapy, The Hague, The Netherlands

2Department of Radiation Oncology, Hotel-Dieu de France St. Joseph University Hospital, Beirut, Lebanon

3Department of Pathology, Erasmus Medical Center, Rotterdam, The Netherlands

4Lonza Ltd. Munchensteinerstrasse 38, CH-4002 Basel, Switzerland

Corresponding Author:
Nabil Khater
Department of Radiation Oncology
Hotel-Dieu de France St. Joseph University Hospital, Beirut, Lebanon
Tel: 9611604350
Fax: 9611604000
E-mail: nabil.khate[email protected]

Received Date: June 23, 2017; Accepted Date: August 01, 2017; Published Date: August 07, 2017

Citation: Khater N, Kap M, Sayah R, Elbers D, Vriesendorp HM (2017) Radiolabeled Immunoglobulin Therapy for Patients with Solid Tumors. J Nucl Med Radiat Ther 8:338. doi: 10.4172/2155-9619.1000338

Copyright: © 2017 Khater N, et al. This is an open-access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.

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Purpose: To test the reactivity of monoclonal murine IgM and IgG for Tenascin-C (TNC) in formalinized solid human tumors tissue samples and to estimate the radiation dose that Yttrium- 90 labeled murine IgM reactive with TNC can deliver to a solid tumor and tumor containing draining lymph nodes.

Materials and Methods: Using Immunohistochemistry (IHC), mouse anti-human TNC IgM and IgG clones were tested for the detection of TNC in formalin fixed biopsies of patients with Glioblastoma multiforme (GBM), adeno carcinoma of the exocrine pancreas (PaCa)-, breast-, colon-, renal-, ovary- prostate carcinoma, cutaneous-, ocular- melanomas, and Ewing Sarcoma. IHC was performed on all tumors with an n=1, except for PaCa and ocular melanomas, n=11. Monte-Carlo simulation and convolution calculations were used to determine the activity of Y-90 required for delivering 100Gy to a 50 × 50 × 50 mm3 water-equivalent tumor model, assuming a homogeneous distribution of the radioimmunoconjugate throughout the model volume.

Results: IHC has confirmed reactivity of IgM with TNC in all of the tested human solid tumors samples except for ocular melanoma. Positive and negative controls of IgM specificity were used. The dosimetry simulation predicted an Yttrium-90 activity of 217 MBq to deliver a dose of 100Gy to the tumor model with a 6 mm sharp dose fall off in surrounding normal tissues.

Conclusion: Loco-regional control of human solid tumors may be obtained with intra-tumoral administration of radiolabeled IgM targeting TNC. In TNC negative solid tumors such as ocular melanoma, other tumor-specific target(s) need to be identified.


Radioimmunotherapy; Y-90; IgM; Intra-tumoral; Intralesional; Tenascin-C


Treatment of human patients with a solid tumor

Approximately 50% of all solid tumor patients receive stateof- the-art local regional therapy with surgery and/or radiotherapy. Approximately half the patients with solid tumors receiving state of the art local therapy survive. They are cured. Approximately 25% of patients recur in the location of the primary tumor, the tumor draining lymph nodes and/or at distance by way of hematogenous metastases. Solid tumor patients with measurable hematogenous metastases before or after surgery/radiation are incurable but might obtain temporary benefit from systemic cancer treatment/chemotherapy [1,2].

Retreatment of a solid tumor

Repeat radiotherapy and/or surgery usually cannot be performed due to tolerance constraints of normal tissues surrounding the recurrence [2]. In those cases, local regional control may be achieved by intra-tumoral administration of a new form of Radiolabeled Immunoglobulin Therapy (RIT) targeting the Tenascin-C (TNC) component of the tumor, which is the subject of this report.

TNC expression in normal and malignant tumors

TNC expression is tightly regulated and generally repressed in healthy tissues. TNC is present in normal human breast and is reexpressed in damaged or infected tissues and in many human solid tumors. TNC occurs in different isoforms which are generated by alternative splicing and these TNC variants are abundantly expressed at the invasive tumor front [3]. TNC reactive IgM and an intra-tumoral route of administration are introduced to avoid off target effects [4-6].

Prior experience with radiolabeled IgG reactive with human TNC

Riva and Reardon [7,8] treated patients with recurrent GBM by administering Iodine-131 labeled IgG reactive with human TNC, in the cyst created by the surgical resection of the recurrence. Survival of patients after I-131-IgG administration was often longer than the tumor response duration after initial treatment with surgical resection, post-op radiation and chemotherapy. The I-131 IgG radiation dose to the recurrence could not be determined accurately at the time and might have been too low for cures. Moreover, the gamma emissions of I-131 are too weak to deliver a homogeneous tumor dose and radioactive iodine is enzymatically removed from carrier molecules and taken up in the thyroid gland of the patient or secreted into the stomach of the patient [4,5].

RIT studies in patients with Hodgkin’s disease and non- Hodgkin’s Lymphoma

In the past, RIT has benefited patients with ‘liquid’ tumors, such as Hodgkin’s disease (HD) and B-cell non-Hodgkin’s lymphoma [5,9-13]. A low intravenous dose of 2 mg of anti-ferritin rabbit IgG labeled with Y-90 can have significant therapeutic effects [4,9-11]. In the absence of accurate dosimetric methods at the time, a positive dose effect curve could only be demonstrated in patients with HD by increasing the amount of Y-90 administered per kg bodyweight of the patient (not body surface area) from 111MBq to 148MBq and subsequently to 185MBq [9,11].

Non-Hodgkin lymphoma patients treated with anti-CD-20 labeled with Y-90 need to receive a high (200 mg) intravenous dose of monoclonal IgG to get tumor shrinkage [12]. Tumor responses are due to immunotherapy as well as radiotherapy, while responses in HD patients are easier to optimize because the tumor response is solely due to radiation [11].

Prior translational research

Translational research demonstrated that stable chelation of Y-90 to tumor-reactive IgM injected directly in a subcutaneous human tumor xenograft (diameter between 0.5-1.5 cm) in nude mice diffused rapidly throughout the tumor. Ninety-five percent of the administered IgM was retained in the tumor, while approximately 5% reached the circulatory system. Human tumor xenografts in nude mice were sterilized in 1 or 2 treatment cycles for more than 200 days, without discernible clinical side-effects [14]. Histology and autoradiography showed Y-90 labeled IgM is soluble in vivo and diffuses through the tumor within three hours with the exception of necrotic areas in the tumor mass. Tumor shrinkage was observed 144 h after administration of Y-90 labeled IgM [5,9,13,14]. In contrast 50% of tumor-reactive IgG administered directly into the tumor was washed out in 2 days [4,9,10,14]. Aggregated albumen labeled with Y-90 did not diffuse through the whole tumor mass. It caused hot and cold spots within the tumor and caused less complete responses than tumor reactive Y-90 labeled IgM [7,9,14].

Comparison of IgM and IgG

Radiolabeled IgM and IgG behave differently in vivo due to differences in size and antigen binding sites (ABS). IgM is a pentamer with a molecular weight (MW) of 950 KDa and 10ABS, while IgG is a dimer with a MW of 165 KDa and 2 ABS. IgM molecules cannot cross the blood-brain-barrier or the blood-tumor- barrier, therefore it can only exert a therapeutic effect, if it is administered directly into a tumor mass. The binding of 2 ABS to TNC in the tumor is dynamic. When both ABS are no longer connected to TNC, tumor-reactive IgG is exported out of the tumor by way of tumor venules within 48 hours. Whereas, the 10 ABS of IgM are rarely all disconnected from the tumor antigen and do not leave the tumor mass because IgM is too big to cross the tumor venule wall. IgM can and does emigrate from the tumor by way of large fenestrations in lymph vessel walls. IgM will stick to tumor contained in first echelon lymph nodes, while IgG does not [14-16].

These observations indicate that both, primary tumor and draining lymph nodes, can be treated with intra-tumoral administration of Y-90 labeled tumor reactive IgM. Y-90 is an exclusive beta emitter with 0.935 MeV average energy, maximum range of 10 mm in water, therapeutic range of near 5 mm and rapid fall-off thereafter.

Materials and Methods


All tissue samples used were taken from the paraffin block archives at the Pathology department of the Erasmus University Medical Center in Rotterdam, The Netherlands. In accordance with the Dutch Code of Conduct for the use of residual tissue in research, the head of the tissue bank of the Erasmus University Rotterdam Medical Center graciously granted permission to use residual tissues for this research. The Human Protein Atlas [17] was consulted to find information on TNC expression in normal tissue. Positive control tissue sections (i.e. a multi tissue block containing; normal tonsil, intestine, liver and pancreas) of 4 μm thickness were subjected to various methods of antigen retrieval (AR). The clones were tested without AR, with protease digestion (0.1% protease K for 5 minutes at room temperature) using DAKO, K1494, Dakocytomation (Denmark), and with heat induced epitope retrieval (HIER) i.e. cooking the sections in a temperature controlled microwave for 15 minutes at 100ºC in a pH9 or pH6 Tris/EDTA buffer. Ten monoclonal IgGs and 10 monoclonal IgMs positive for human recombinant TNC in Western blots were provided by ProMab Biotechnologies Inc. (Richmond, CA, USA). All 20 anti-TNC clones; 10 IgG and 10 IgM were diluted 1:10, 1:100 and 1:1000 to determine the optimal dilution. As negative control, the primary antibody was omitted. Slides were incubated with the primary antibodies for 30 minutes at room temperature and with diaminobenzidine for 10 minutes at room temperature using DAKO REAL EnVison, K5007 (Denmark) to detect the tissue bound primary antibody. The sections were counterstained with hematoxylin for 1 minute and cover slipped. The optimal TNC staining, hence the optimal protocol, was selected by comparing the TNC staining results to the images in the Protein Atlas data base of normal tissues [17].

A tissue micro array (TMA) consisting of pancreas carcinoma samples of 11 different patients was made. A pathologist marked the tumor sites on the hematoxylin and eosin stain slide of the corresponding paraffin block. By use of a Beecher manual tissue arrayer, 1 mm cores were taken from the selected tumor blocks (1 core from each block) and gathered in a receptor block TMA. Sections of 4 μm thickness were cut and immunohistochemistry (IHC) was performed using the optimized protocol. On one slide 11 pancreas carcinoma samples were stained, all under the same conditions to ensure differences in TNC expression (staining intensity) are not related to inter-assay variability. Digital images of all relevant slides were exported from scanned slides (Hamamatsu Nanozoomer, Hamamatsu, Germany).


A convolution of the bio-distribution with the dose point kernel (DPK) will result in a 3D dose distribution [18]. For computational purposes a kernel with finite voxel size is required and termed herein dose voxel kernel (DVK). Using the MCNPX Monte Carlo code version 2.6 c [19], the DVK of Y-90 in water was simulated in Cartesian cubical geometry at 0.5 mm, 1 mm and 3 mm voxel sizes, and the DPK was simulated in concentric shells geometry for a near-point- source of 20 μm radius with 20 μm shell thicknesses. The DVK’s at 0.5 mm and 1 mm voxel sizes were used for convolution computations, and the DVK at 3 mm voxel size was used to validate the results by comparison with MIRD-17 S values [20] also calculated at a voxel size of 3 mm. The DPK was used to calculate the radius of the sphere (X90) within which 90% of the dose is absorbed. For the 1 mm voxel DVK, the source size was modeled at 1 × 1 × 1 mm3 located at the center of cubic voxel geometry. Source strength was modeled homogenously distributed inside the source. Tallies were averaged in each voxel, and values were approximated to represent dose at the center of each voxel, in a volume spanning 25 × 25 × 25 mm3. In concentric shells geometry, the point source was modeled as a spherical source with 20 μm radius. Energy was tallied in concentric shells around the source with shell thicknesses constant at 20 μm. The outer shell radius was set to 12 mm; the shell tally was approximated to represent dose at mid-distance from outer and inner shell boundaries. The medium in both geometries was set to water. The spectrum of Y-90 was extracted from Cross et al. [21] and modeled with equally spaced energy bins of 0.25 MeV. The electron and photon cutoff energy set to 1 keV. Photons and electrons were tracked and F6 tallies (electron+photon) were used to calculate the dose in each voxel. Ten million histories were followed. The 3D DVK was regenerated using a MATLAB script (The MathWorks, Natick, MA) in a volume of 25 × 25 × 25 mm3 with a 1 mm voxel size. A hypothetical planning target volume (PTV) was also modeled in the script as a 50 × 50 × 50 mm3 of water equivalent material with a 1 mm voxel size, a uniform biodistribution of 37Bq/voxel (1nCi/voxel), and surrounded by water. Convolution of the PTV with the 3D DVK was performed using MATLAB to estimate the activity of Y-90 needed to deliver a dose of 100Gy to the PTV. The matrix dimension resulting from the full convolution of the PTV with the DVK is 74 × 74 × 74 mm3, permitting the recording of dose in the gradient just outside the PTV in addition to the dose within the PTV. The same calculations were repeated for 0.5 mm voxel kernel and 0.5 mm voxel PTV to assess voxel size effect on dosimetry. The convolution will yield an initial dose rate (? ) decaying exponentially with the half-life (T1/2) (64 h for Y-90).

The integral dose inside the PTV (?) was calculated as follows:

Ds=?(1.44)T1/2 (1)

Where: (1.44)T1/2 is the integral decay time of Y-90 inside the PTV [22].

The total activity inside the PTV used in this simulation As was calculated as follows:

As=V.a (2)


• V is the PTV volume in voxels

• a is the activity per voxel (37 Bq)

The total activity AT required to deliver an integral total dose DT of 100 Gy to the PTV calculated as follows:



IHC studies in formalin fixed tissues of various human tumors

Eight out of 10 monoclonal IgG’s and 6 out of 10 IgM’s recognized TNC in human tissues by IHC. One of the 6 monoclonal IgM’s that reacted with TNC in human tissues by IHC was selected for making a master cell bank. The expression patterns found in normal tonsil, intestine, liver and pancreas tissue resembled the patterns found in the human protein atlas [17] confirming the specificity for TNC for both IgG and IgM.

TNC expression in a GBM resection specimen

Mouse monoclonal IgG and IgM reacted with TNC in the extracellular matrix surrounding the tumor cells and in some individual cells (brown staining in Figure 1). The monoclonal IgM anti- TNC has a 10-fold lower titer than the monoclonal IgG. Mouse spleen cells were harvested after 6 weekly immunizations. IgG will increase in affinity and titer after each immunization. In contrast IgM titers decrease more rapidly overtime, and repeat immunizations will each time produce the same spike of antigen reactive IgM, with the same low affinity [23] (Figure 1).


Figure 1: TNC expression in GBM. Dark staining areas contain GBM cells. Optimal IgG titer is 1:100. Optimal IgM titer is 1:10.

TNC expression in adenocarcinoma of the exocrine pancreas (PaCa).

IgG and IgM reacted with TNC in 11/11 patients with PaCa. TNC expression is quite heterogeneous as observed in 4 patient samples shown in Figure 2.


Figure 2: TNC expression in 4 human pancreatic tumors. Dark areas indicate the presence of TNC.

TNC expression in other human solid tumors

IgG and IgM reacted with TNC in one sample of colon-, renal- (Grawitz tumor), prostate-, breast- carcinoma, Ewing sarcoma, ovarian cancer and melanoma. Eleven different patient samples of ocular melanoma were TNC-negative. In most other tumors tested TNC is detected in the connective tissue surrounding the tumor cells. In the breast carcinoma sample the tumor cells themselves contain TNC (Figure 3).


Figure 3: TNC expression in several human solid tumors. Dark areas indicate the presence of TNC.

Y-90 Dose Point and DVK

Good agreement is observed between the four simulation geometries presented and MIRD-17 (Figure 4). The 3 mm DVK is almost identical to the MIRD-17 S values also calculated at 3 mm voxel size. Due to voxel volume averaging, the dose rate increases with decreasing voxel size at distances less than 2 mm from the source center and decreases with increasing voxel size at distances greater than 6 mm from the source. The DPK exhibits a high dose rate in proximity of a 20 μm point source due to the singularity problem. Beyond 10 mm, the dose contribution is nil. X90 was evaluated from the concentric shells simulation to be 0.533 cm, which compares well with 5.34 mm reported by Simpkin [24] and 5.4 mm reported by Botta [25]. Consequently, this comparison appears to justify the use of simulated kernels in the dose convolution calculations (Figures 4 and 5).


Figure 4: Y90 DVK’s of 0.5 mm, 1 mm and 3 mm voxel sizes and DPK for a 20 μm point source compared to MIRD-17 [20].


Figure 5: Dose rate (mGy/hr) distribution within the PTV model with 1mm voxel size containing 37Bq/voxel. The computed dose rate at the core is 23.2 mGy/hr (red area); then tapers to 0 mGy/h (outer edge of green area) over a distance of 6 mm.

Dosimetry estimation

The convolution of the 1 mm voxel DVK with the PTV at the assumed biodistribution of 37 Bq/voxel (1nCi/voxel), yielded an initial dose rate (?) of 23.2 mGy/hr. ? is homogeneous inside the PTV with a sharp falloff to 0 at 6 mm outside the PTV (Figure 5).

The integral dose inside the PTV (Ds) was 2.13 Gy calculated using equation (1).

The total activity inside the PTV used in this simulation (As) was 4.625 MBq calculated using equation (2).

The total activity (AT) required to deliver an integral total dose (DT) of 100Gy to the PTV was 217 MBq calculated using equation (3).

Calculations were repeated for the same PTV model and DVK but with 0.5 mm voxel size, yielding AT value of 226 MBq (Table 1); not significantly different from the 1 mm voxel size calculations. In this simulation, it is assumed that no activity is metabolized biologically. In vivo, immune complexes of antigen and immunoglobulin are catabolized slower than the half-life of the bare, not antigen binding, immunoglobulin [5] (See “Pharmaco-kinetics and bio-distribution” and “Pharmaco-vigilance and patient safety” sections for effective halflife and residence time determination).

Voxel size (mm)3 V(voxels) ?(1)(mGy/hr) DS(2)(Gy) AT(3) (MBq)
(1mm)3 1,25,000 23.2 2.13 217
(0.5mm)3 10,00,000 177 16.3 226

Table 1: PTV model simulated dosimetry for 2 different voxel sizes.


Results reported in this communication, prior translational animal studies, and RIT studies in patients with end-stage Hodgkin's disease [4-6,9,26], suggest that a high 'targeted' dose with sharp dose fall-off in adjacent normal tissues may be delivered to patient with solid tumors via intra-tumoral RIT using Y-90 labeled murine IgM against TNC. TNC appears to be a good target as it is abundant in most solid tumors tested and has limited expression in healthy normal tissues.

Radiation biology

The dose rate after RIT decreases exponentially with the half-life of the radionuclide. In general, biological effects of radiation; such as cell killing, tend to decrease with lower dose rates [27,28]. However, cells irradiated at low dose rates tend to collect in the G2M phase of the cell cycle, in which, the DNA condenses, and lethal double strand DNA breaks become more frequent; double DNA strand breaks are the dominant killing mechanism for tumors as well as normal cells. As a result, Gray for Gray low dose rate RIT and daily fractions of external beam radiation therapy (EBRT) doses are almost equally effective. Theoretically several RIT cycles could be sufficient to obtaining local regional control of a solid tumor without serious side effects. This makes this therapy much more effective than EBRT in terms of escalating the dose while maintaining normal tissue tolerance. Hence new possibilities will be opened for treating tumors known to be nonresponsive to EBRT.

Pharmaco-kinetics and bio-distribution

In prior experiments with human tumor xenograft bearing nude mice the administration of In-111 and Y-90 labeled immunoglobulins showed similar pharmacokinetics and biodistributions. This justifies the use of the 3D In-111 distribution as an accurate predictor for the in vivo Y-90 distribution [4,5,9,11,13,26]. In-111 is a gamma-emitter with 67 h half-life; close to that of Y-90 (64 h). It has two energy peaks that can be accurately detected using properly collimated gamma camera. Serial SPECT imaging on 3,24,48 and 72 hours after administration will verify the residence time in vivo. It also allows the determination of the bio-distribution and the effective half-life, hence permitting patientspecific dosimetry, where the SPECT measured effective half-life would be used for dose computation in equation (1). Y-90 linked and In-111 linked proteins can only be expected to provide similar biodistributions if a stable linker with 8 co- ordination points is used, such as 2B, 3M, DTPA [29]. Other clinically used chelates without carbon backbone stabilization have only 7 co-ordination points, thereby chelated In-111 which only needs 6 co-ordination points would be bound in a stable manner, but Y-90, a bone seeker, needs 8 co-ordination points. With chelates having only 7 co-ordinates points, Y-90 would be released in vivo, which will cause serious bone marrow damage in human cancer patients.

Pharmaco-vigilance and patient safety

To ascertain that only patients who might benefit from this therapy will be selected for treatment, radiolabeled IgM reactive with human TNC should be delivered in two steps [4,5,9,11,13]:

Step 1: Intra-tumoral administration of 2 mg of a mouse monoclonal IgM labeled with Indium-111 (In-111) reactive with TNC. This provides two important advantages:

1. In vivo determination of the location, stability and residence time of the radio-immuno-conjugate. Patients with insufficient radio-immuno-conjugate in the tumor or too much radio-immunoconjugate in critical normal tissues will not benefit from step 2 RIT and will not proceed to step 2.

2. Treatment planning and patient-specific dosimetry to determine the activity required and resulting dose distribution. The In-111 biodistribution acting as a predictor of the Y-90 biodistribution will be used in the dose calculation. The dosimetry would be specific to the tumor and normal tissue volumes of the individual patient. More accurate normal tissue and solid tumor tissue dose response curves will become available. The 1D and 2D measures for tumor staging and tumor response can be replaced by 3D (cc, tumor volume measures).

Step 2: One week after successful In-111 labeled IgM administration, 2 mg of Y-90 labeled IgM reactive with TNC will be administered directly into the tumor.

Clinical radio-pharmacy

The radioimmunoconjugate (RIC) administered to human patients should always be protected from radiolysis by adding endotoxin-free clinical grade Human Serum Albumin. Once radiolabeled, the IgM should be administered within 4 h. Radiolysis of the In-111 or Y-90 labeled RIC has not been observed in the radio-pharmacy by instant or thin layer chromatography. This was demonstrated in more than 200 RIT cycles in 90 patients with 4-5 sequential blood samples/patient taken in the first week after administration [5,11,13]. In vivo radiolysis of the In-111 labeled IgG has occurred in patients with circulating antibodies against murine IgG. In-111 is not a bone-seeker like Y-90, but secreted by way of bile into the digestive tract [11].

Optimization of the radioimmunoconjugate

The replacement of low TNC affinity genes in the variable region of the IgM with high affinity variable genes of anti TNC IgG will allow for a more economical smaller mg protein dose per RIT administration [23]. Humanization of the murine IgM will reduce anti-antibody formation and lower the risks of using this IgM in human patients more than once [30]. The murine IgM will be assessed for post-translational motifs (PTMs) which could increase the risks in recombinant manufacturing and decrease its shelf life. Removal of risky PTMs can reduce aggregation and increase stability and shelf life of the IgM-DTPA [31-33].

Proposed human studies

Intra-tumoral administration of Y-90 labeled IgM reactive with TNC should be explored in patients with poor prognosis solid tumors such as recurring GBM and PaCa. Almost all GBM patients succumb to their disease within 4 years after the initial diagnosis or within 2 years after a recurrence. Most GBMs recur close to the location of the original mass. Dose escalation studies in patients with a recurrent GBM will have to start at a low dose because all of them will have received high EBRT dose previously. Half of the patients with a resectable PaCa are cured by radical surgery with a surgical mortality rate of 2-4% [34]. The overall long term survival rate of all PaCa patients is <10%. Risk factors for recurrent PaCa patients after radical surgery are regional lymph nodes positive for PaCa and/or close or positive margins in the surgical resection specimen. In this report formalinized tumor biopsies of 11 out of 11 patients with PaCa tested positive for TNC in their tumor matrix. Pre-op use of intra-tumoral IgM reactive with TNC in patients with borderline operable PaCa might increase local regional control of PaCa and increase the applicability of the only curative option for PaCa at this time; radical surgery [34]. The inhomogeneous distribution of TNC in the PaCa samples tested in this study will not lead to cold spots in the tumor volume due to the relatively long therapeutic range (X90=5.33 mm) of Y-90. If proof of principle can be obtained in RIT studies of GBM and PaCa patients, other solid tumor patients with TNC in their tumor matrix can be studied and a search for other tumor matrix antigens in TNC negative tumor, such as ocular melanoma, should be made.


The IHC results provided proof that monoclonal IgM and IgG can recognize TNC in several human tumor tissue samples including GBM and PaCa. IgG has higher affinity for TNC than IgM. The tumor model dosimetry simulation estimated the Y-90 activity required in a therapeutic RIT cycle to deliver the tumor targeted high dose while sparing normal tissues. This study in combination with prior translational animal research indicate that loco-regional control of human solid tumors may be obtained with intra-tumoral administration of Y90-labeled tumor reactive IgM. The exploration of this therapy in short single arm Phase 2 studies in patients with thus far non-curable tumors such as GBM and PaCa, will provide information on how to optimize survival or even cure.


Developing new applications for Radiolabeled Immunoglobulin Therapy requires a multidisciplinary team. Huib Vriesendorp wants to acknowledge his long standing collaboration with Syed M Quadri, PhD, an excellent friend, educator and chemist and Paul Borchard, PhD, for their valuable contributions to the field of radioimmunotherapy. This research did not receive any specific grant from funding agencies in the public, commercial, or not-for-profit sectors.


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