WO2011057146A1 - Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof - Google Patents
Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof Download PDFInfo
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- A—HUMAN NECESSITIES
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/0515—Magnetic particle imaging
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
- G01N33/574—Immunoassay; Biospecific binding assay; Materials therefor for cancer
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/242—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
- A61B5/412—Detecting or monitoring sepsis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
- A61B5/414—Evaluating particular organs or parts of the immune or lymphatic systems
- A61B5/415—Evaluating particular organs or parts of the immune or lymphatic systems the glands, e.g. tonsils, adenoids or thymus
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
- A61B5/414—Evaluating particular organs or parts of the immune or lymphatic systems
- A61B5/418—Evaluating particular organs or parts of the immune or lymphatic systems lymph vessels, ducts or nodes
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/24—Arrangements or instruments for measuring magnetic variables involving magnetic resonance for measuring direction or magnitude of magnetic fields or magnetic flux
- G01R33/26—Arrangements or instruments for measuring magnetic variables involving magnetic resonance for measuring direction or magnitude of magnetic fields or magnetic flux using optical pumping
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/39—Markers, e.g. radio-opaque or breast lesions markers
- A61B2090/3954—Markers, e.g. radio-opaque or breast lesions markers magnetic, e.g. NMR or MRI
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/0285—Nanoscale sensors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
- A61B5/414—Evaluating particular organs or parts of the immune or lymphatic systems
- A61B5/416—Evaluating particular organs or parts of the immune or lymphatic systems the spleen
Definitions
- This invention relates to the in vivo detection and measurement of cells or substances using targeted nanoparticles and magnetic relaxation measurements, and is particularly useful in detecting and measuring cancer cells in humans.
- Early detection of disease allows the maximum likel ihood of successful treatment and recovery. Furthermore, early detection and localization of the disease permits directed therapy to the site of the disease optimizing the efficiency of the treatment. With an appropriate detection device, the treatment can be monitored, further increasing the efficacy of the applied drugs or other forms of therapy. The ability to target specific diseases can also improve treatment outcomes. Early detection and localization of cancer, the second leading cause of death in the US, can improve patient outcomes.
- the most common methods used for clinical purposes for detection of cancer are all nonspecific, i.e., they cannot distinguish between cancerous or benign tumors and none lead to 100% accurate detection. The available methods all have disadvantages and weaknesses, resulting in high rates of false diagnosis and too low a rate of positive diagnosis, together leading to increased mortality rates.
- the most common clinical modalities presently available are: (1) X-ray
- MRI magnetic resonance imaging
- PET ultrasound scanning with (4) positron-emission tomography
- the measurement of X-ray attenuation provides information on the density of the intervening medium and is FDA approved and the most common device used to detect various forms of disease and, in particular, cancer. It is also responsible for many false-negative and false-positive results. Early stage cancer tumors can be detected but without specificity with regard to benign or cancerous tumors. Artifacts can be caused by healthy tissue and give rise to false positive results. Although the dose is low, there is increasing concern about the exposure to X-rays and radiation in general. Overall, the number of false positives in x-ray imaging of cancer remains high and the x-ray method cannot detect early-stage tumors.
- Ultrasound is used to provide a second method for imaging tumors. Ultrasound has excellent contrast resolution but suffers from diminished spatial resolution compared to x-rays and other imaging techniques. Ultrasound is not currently approved by the FDA as a primary screening tool for cancer but is normally used as a follow up to investigate any abnormalities detected during routine. It is a tool often used to confirm suspect areas in x-ray images of breast and ovarian cancer.
- MRI is used to follow up on potential problem areas seen during x-ray scans; however, the expense of a MRI scan often prohibits its use. MRI can detect small abnormalities in tissue and is also useful in determining if cancer has metastasized.
- Dynamic Contrast Enhanced (DCE) MRI potentially distinguishes between benign and cancerous tumors but produces a number of false positives.
- the expense of MRI limits its application as a screening tool.
- MRI imaging of cancer often uses magnetic nanoparticles as contrast agents and is an accepted protocol providing standards for the injection of such nanoparticles.
- Intravascular MRI contrast agents at a dose of 2mg/kg of nanoparticle weight have been used to detect metastatic lesions.
- the present invention provides apparatuses and methods to detect cells or substances such as cancer cells in tissue.
- the system comprises a magnetic system, including a magnetic field generator that imposes a known magnetic field on tissue of the subject, magnetizing targeted paramagnetic nanoparticles bound to the cells or substance of interest; and including a sensitive magnetic sensor that can detect the residual magnetic field as the magnetization of the nanoparticles decays.
- An example magnetic system comprises a superconducting quantum interference device sensor comprising a magnetic pulser, adapted to apply a uniform magnetizing pulse field to a cancer tissue of a patient placed on a measurement stage; and a remnant magnetic field detector, adapted to detect and image the residual magnetic field produced by the applied pulsed field.
- the magnetic pulser can comprise a pair of Helmholtz coils.
- the remnant magnetic field detector can comprise an array of gradiometers.
- Another example magnetic system comprises an atomic magnetometer and an array of atomic gradiometers - very sensitive magnetic field sensors that can be used to measure extremely weak magnetic fields based on the Larmor precession of atoms in a magnetic field.
- the atomic magnetometer and an array of atomic gradiometers - very sensitive magnetic field sensors that can be used to measure extremely weak magnetic fields based on the Larmor precession of atoms in a magnetic field.
- the atomic magnetometer and an array of atomic gradiometers - very sensitive magnetic field sensors that can be used to measure extremely weak magnetic fields based on the Larmor precession of atoms in a magnetic field.
- the atomic magnetometer and an array of atomic gradiometers - very sensitive magnetic field sensors that can be used to measure extremely weak magnetic fields based on the Larmor precession of atoms in a magnetic
- magnetometer comprises a chip set containing a small cavity containing an atomic vapor cell.
- This vapor cell contains b atoms, and is optically pumped by circularly polarized laser beam.
- the atoms go through a Larmor precession and the frequency of this precession causes a change in the index of refraction of the vapor in response to an applied magnetic field.
- a second laser can be used as a measuring field for this change in refraction using a set of gratings to measure interference pattern changes as the applied magnetic field changes.
- the vapor cells can be single or arranged in a gradiometer configuration to measure the changes in field as a function of distance.
- a method comprises providing the magnetic system; injecting a plurality of targeted (e.g., labeled with an antibody) paramagnetic nanoparticles into a subject for specific binding to the cancer cells or other cells or substance of interest; applying a known (e.g., uniform) magnetizing pulse field to magnetize the nanoparticles in the subject tissue; and detecting the residual magnetic field of the magnetized nanoparticles thereby providing an image of the nanoparticles bound to the cancer tissue of the patient.
- the targeted paramagnetic nanoparticle can comprise a magnetic core coated with a biocompatible coating to which is attached at least one specific antibody.
- the magnetic core can comprise a ferromagnetic material, such as iron oxide. Examples of suitable targeting agents such as antibodies are described below.
- FIG. 1 is a schematic illustration of an example preparation of tissue of a subject for measurement according to the present invention.
- Fig. 2(a,b,c,d) provide a schematic illustration of an example measurement in accord with the present invention.
- Fig. 3 is a schematic illustration of measurements from the process described in connection with Fig. 2.
- Fig. 4 is a schematic illustration of an apparatus suitable for use in the present invention.
- Fig. 5 is a schematic illustration of an exemplary apparatus using superconducting quantum interference device (SQUID) magnetic sensors.
- Fig. 6 is a schematic illustration of an exemplary SQUID sensor apparatus that can be used for human cancer examinations.
- SQUID superconducting quantum interference device
- Fig. 7 is a schematic illustration and photo of an atomic magnetometer for weak field
- Figure 8 is schematic illustration of a magnetic nanoparticle with biocompatible coating and attached antibodies for targeting specific cells.
- Fig. 9 is a depiction of the number of Her2 sites per cell calculated by comparison to a range of microspheres with known binding capacities.
- Fig. 10 is an illustration of magnetic moments of two breast cancer cell lines, MCF7/HE 218 and MDA-MB-231 measured as function of time after incubating with HER2/neu antibodies and nanoparticles.
- Fig. 11 is an illustration of the magnetic moments of cell samples measured as function of number of cells by pipetting cells down by factors of two.
- Fig. 13 is a photo of a nude mouse under a SQUID system.
- Fig. 14 contains position confidence plots obtained from mouse tumors.
- Fig. 15 is an illustration of the magnetic contour lines observed for 35 different measurement sites
- Fig. 16 is an illustration of the time course of the measurements for the two mice and both tumors of each mouse.
- Fig. 17 is an illustration of the results of these measurements and show very good agreement with the in-vivo measurements on the live mouse.
- Fig.18 is an illustration of the 2-dimensional 95% confidence limit for the locations of the two tumors superimposed on the actual tumors of the mouse.
- Fig. 19 is a photo of the histology of tumors after extraction.
- Fig. 20 is an illustration of an ovarian cancer showing the growth of the tumor on the ovary.
- Fig. 21 is photograph of a full-size ovarian phantom placed under a SQUID sensor apparatus at a distance that would be typical of a patient subject.
- Fig. 22 is an illustration of the results of sensitivity studies for live ovarian cells inserted into the phantom shown in Fig. 21.
- Fig. 23 is an illustration of confirmation of antibody sites for these cells using flow cytometry.
- Fig. 24 is an illustration of magnetic moments from magnetic nanoparticles (from Ocean Nanotech) attached to ovarian human cancer tumors in the live mouse.
- Fig. 25 is a photograph of a mouse used to verify that the SQUID sensor method works in-vivo along with magnetic contour fields from the mouse.
- Fig. 26 is a graph of a measurement of the magnetic moment in a SQUID sensor system as a function of time for incubation of attaching magnetic nanoparticles to lymphoma cell lines.
- Fig. 27 is an illustration of the results of the flow cytometric measurements of S cells from the lymphatic system in determining the number of sites available for nanoparticles and detection by the SQUID sensors.
- Fig. 28 is a histology slice from a patient with Hodgkin's Disease.
- the term "detection" is used for brevity; the invention can provide for the detection of the presence of cells or substances, measurement of the number of cells or amount of substance, determination of the location of cells or substance, determination of the change or rate of change in the preceding, and similar determinations, all of which are included in the term
- FIG. 1 is a schematic illustration of an example preparation of tissue of a subject for measurement according to the present invention.
- the illustrations in the figure are highly simplified and intended for ease of explanation only, and are not intended to represent the actual shapes, sizes, proportions, or complexities of the actual materials involved.
- a portion of the tissue 11, e.g., an organ to be investigated, or a known or suspected tumor site comprises some cells of the type of interest (shown in the figure as circles with "V" shaped structures around the periphery) and some cells of other types (shown in the figure as ovals with rectangular structures around the periphery).
- a plurality of magnetic nanoparticles 12 is provided, shown in the figure as small circles.
- a plurality of targeting molecules 13 is also provided, shown in the figure as small triangles. The nanoparticles and targeting molecules are combined (or conjugated), forming targeted nanoparticles 14.
- the targeted nanoparticles can then be introduced to the tissue 15.
- Cells of the type of interest have binding sites or other affinities for the targeting molecule, illustrated in the figure by "V" shaped structures around the periphery of such cells.
- the targeting molecules attach to the cells of the type of interest, illustrated in the figure by the triangular targeting molecules situated within the "V" shaped structures.
- each cell will have a large number of such binding or affinity sites.
- Cells of other types do not have such binding sites or affinities, illustrated in the figure by ovals with no targeted nanoparticles attached.
- Targeted nanoparticles that do not bind to cells are left free in the prepared sample, illustrated in the figure by small circles with attached triangles that are not connected with any specific cell. [0017] Fig.
- FIG. 2(a,b,c,d) provide a schematic illustration of an example measurement in accord with the present invention.
- Fig. 2a the tissue is as in Fig. 1, with the addition of arrows near each nanoparticle.
- the arrows are representative of the magnetization of each nanoparticle, and indicate that the magnetization of the nanoparticles in the tissue is random (in the figure, the arrows are shown in one of four directions for ease of illustration only; in practice the magnetization can have any direction).
- FIG. 2b an external magnetic field (represented by the outlined arrow at the lower right of the figure) is applied.
- the magnetization of the nanoparticles in response to the applied magnetic field is now uniform, represented in the figure by all the magnetization arrows pointing in the same direction.
- Fig. 2c illustrates the tissue a short time after the magnetic field is removed.
- the nanoparticles not bound to cells are free to move by Brownian motion, and their magnetization rapidly returns to random, represented in the figure by the magnetization arrows of the unbound nanoparticles pointing in various directions.
- the nanoparticles bound to cells are inhibited from such physical motion and hence their magnetization remains substantially the same as when in the presence of the applied magnetic field.
- Fig. 2d illustrates the prepared sample a longer time after removal of the applied magnetic field. The magnetization of the bound nanoparticles has by now also returned to random.
- Fig. 3 is a schematic illustration of measurements from the process described in connection with Fig. 2. Magnetic field is shown as a function of time in a simplified presentation for ease of illustration; in actual practice the units, scales, and shapes of the signals can be different and more complex.
- the nanoparticle magnetization is random and the external magnetic field is applied. After that time, the
- the magnetization can then be measured as the bound nanoparticles transition from uniform to random magnetization, corresponding to the state of Fig. 2d.
- the characteristics of the measurement magnetization from the state of Fig. 2c to that of Fig. 2d are related to the number of bound nanparticles in the sample, and hence to the number of cells of the type of interest in the sample.
- FIG. 4 is a schematic illustration of an apparatus suitable for use in the present invention.
- a subject stage 41 is configured to dispose the subject in an effective relationship to the rest of the apparatus.
- a magnetizing system 42 for example Helmholtz coils, mounts relative to the subject stage so that the magnetizing system can apply a magnetic field to the sample.
- a magnetic sensor system 43 mounts relative to the subject stage so that it can sense the small magnetic fields associated with the magnetized nanoparticles.
- the system is controlled and the sensor data analyzed by a control and analysis system 44; for example by a computer with appropriate programming.
- FIG. 5 is a schematic illustration of an exemplary apparatus using superconducting quantum interference device (SQUID) magnetic sensors.
- a liquid helium reservoir dewar 51 at the top of the picture maintains the temperature of the SQUID sensors.
- SQUID 2nd-order axial gradiometers are contained in a white snout 52 protruding through a support frame 53. There are seven gradiometers contained within this exemplary snout; one in the center and 6 in a circle of 2.15 cm radius. Each gradiometer is inductively coupled to a low temperature SQUID.
- Two circular coils 54 form a Helmholtz pair that can provide a magnetizing pulsed field for the nanoparticles.
- the uniform field produced by these coils can be varied but typically is 40 to 50 Gauss and the pulse length is typically 300 - 800 msec.
- a wooden frame supports the SQUID and the measurement platform as well as the magnetizing coils.
- the non-magnetic support system comprises a 3- dimensional stage 55 that can be constructed with no metal components, e.g., of plastic.
- the upper two black knobs control the x-y stage movements over a +/-1 cm range and the lower knob is used to raise and lower the measurement stage over a 20 cm range.
- a sample holder can be inserted onto the stage that can contain live subjects such as mice or other small animals.
- FIG. 6 is a schematic illustration of an exemplary SQUID sensor apparatus that can be used for human cancer examinations.
- a wooden structure 63 can be similar to the support frame shown in Fig. 5.
- the measurement stage can be replaced by a bed 65 for patient placement.
- Two larger Helmholtz coils 64 comprise the wooden circular forms above and below the bed. These larger coils can be used to generate a uniform pulse field and magnetize the magnetic nanoparticles that have been injected into the patient.
- the currents can be modified, e.g., increased, from those used in the apparatus shown in Fig. 5 to again produce fields in the range of 40 to 50 Gauss.
- a SQUID dewar 61 with an array of magnetic gradiometers can be used to measure the residual magnetic field change produced by the magnetized nanoparticles.
- Fig. 7 is a schematic and photo of an atomic magnetometer for weak field measurements.
- This device is miniaturized by using microchip fabrication methods and multiple units can be placed side-by-side to form an array of sensors.
- the operation of the magnetometer is through application of a laser light beam applied through an optical fiber.
- This beam pumps the heated b gas in the vapor cell into specific atomic states.
- the beam is first elliptically polarized and collimated into the vapor cell.
- a mirror reflects this beam back through the cell and lens into a polarization analyzer.
- a magnetic field applied perpendicular to the length of the magnetometer changes the index of refraction of the gas in the cell, changing the polarization of the light through the cell.
- the change in polarization yields the magnitude of the applied magnetic field.
- the pumping laser supplies multiple fiber optic cables and is thus used for multiple magnetometers.
- An array of these magnetometers for relaxometry measurements can comprise 7 vapor cells placed with one in the center surrounded by 6 more.
- the applied field from the magnetizing coils is perpendicular to the arrangement shown in Fig. 5 in order to induce the maximum observable magnetic moments into the nanoparticles.
- the photo at the bottom of Fig. 7 shows an exemplary physical arrangement and size of the atomic magnetometer for application with the present invention.
- the sensitivity of the device shown is 0.16fT/VHz, compared to sensitivity of an exemplary SQUID system as shown in Fig. 5 of 1.0pT/VHz (lOOOfT/VHz).
- Atomic magnetometers require no cryogenic coolant which can make them desirable for clinical applications where such coolants, in particular liquid helium, are not always readily obtainable.
- mammography For breast cancer, the current method of choice for screening and detection is mammography. While mammography has led to a significant improvement in our ability to detect breast cancer earlier, it still suffers from the inability to distinguish between benign and malignant lesions, difficulty in detecting tumors in dense and scarred breast tissue, and fails to detect 10-30% of breast cancers.
- the use of magnetic nanoparticles conjugated to tumor-specific reagents combined with detection of these particles through measurement of their relaxing fields represents a promising new technology that has the potential to improve our ability to detect tumors earlier. Furthermore, detection of targeted magnetic nanoparticles using weak field sensors is fast and is can be more sensitive than M I detection because only particles bound to their target cells are detected.
- FIG. 8 is schematic illustration of a magnetic nanoparticle with biocompatible coating and attached antibodies for targeting specific cells.
- HER2 Antibodies (Ab) that are specific to 30-40% of breast cancers.
- the nanoparticles had coatings containing Carboxyl groups and a Sulfo-NHS method is used to conjugate the nanoparticles to the antibodies.
- Flow cytometry performed for breast cancer cell lines MCF7, MCF7/Her2-18 (MCF7 clone stably transfected with Her2), BT474, and MDA-MB-231. Number of Her2 binding sites determined by flow cytometry, Anti-Her2 antibodies conjugated to the fluorescent probe FITC.
- MCF7 cells engineered to overexpress Her2-18 have 11 x 106Her2 binding sites/cell
- BT-474 have 2.8 x 106
- MCF7 0.18 x 106 MDA-MB-231 0.11 x 106.
- Non-breast cell lines have ⁇ 4000 Her2 binding sites/cell.
- Fig. 10 is a graph of a measurement of the magnetic moment in the SQUID sensor system as a function of time for incubation of attaching magnetic nanoparticles (from Ocean Nanotech) to breast cancer cell lines.
- the magnetic nanoparticles were coated with a carboxyl biocompatible coating and were then conjugated to the Her2/neu antibody. This antibody is specific to approximately 30% of breast cancer cells in humans.
- the labeled magnetic nanoparticles were inserted into vials containing live cancer cells and the magnetic moments of the vial measured at various times ranging from one minute to 16 minutes. The zero time point is the magnetic moment of the vial of nanoparticles before adding to the cells.
- the lack of magnetic moment for the unmixed particles is a demonstration that unbound particles give no magnetic signal with this SQUID imaging method.
- the magnetic moments increase rapidly and saturate indicating that the cells have collected on their surfaces the maximum number of nanoparticles possible in one to two minutes.
- the top curve is for the breast cancer cell line, MCF7/Her218 that is known to be very specific for the Her2/neu antibody and the large magnitude of the magnetic signal verifies this.
- the breast cancer cell line, MDA-MB-231 is also positive for Her2/neu but with much fewer sites for the antibody targeted nanoparticles to attach to. The smaller magnitudes are also indicative of this trend.
- the CHO cell line is non-specific to Her2/neu and gives substantially smaller magnetic moments after incubation.
- Fig. 11 is an illustration of the magnetic moments of cell samples measured as function of number of cells by pipetting cells down by factors of two. The demonstrated sensitivity is 100,000 cells forMCF7 cells and Ocean nanoparticles, for cells 3.5 cm from the sensor. There are
- FIG. 13 is a photo of a nude mouse under a SQUID system.
- a mouse was injected with human MCF7 cells two weeks previously in two places. These cells then produced human tumors on the flanks of the mouse; one such tumor is visible behind the right ear of the mouse.
- the mouse was anesthetized through the tube over its mouth. Labeled magnetic nanoparticles were injected into the mouse at this stage either by tail, inter-peritoneal, or inter- tumoral injections. Subsequent to injections, the mouse was placed under the sensor system as shown and a magnetizing pulse was applied and the resulting magnetic moments of the injected particles were measured.
- mice resided on the stage shown in Fig. 5 and could be moved to several positions under the sensor system to obtain more spatial information. Measurements were made as a function of time to determine how fast the particles were taken up from the blood stream and how fast phagocytosis occurred with the particles ending up in the liver. The mouse was typically placed at five stage positions under the 7-channel SQUID system to obtain 35 spatial locations.
- Fig. 14 contains position confidence plots obtained from mouse tumors. Left sphere is from left tumor that is ⁇ 2 x right tumor in magnetic moment (see below). Positions calculated by two dipole least squares method to extract magnetic moments and positions. Moments determine number of labeled cells in tumors.
- Figs. 16, 17, 18 The SQUID system results for in-vivo measurements on living animals are shown in Figs. 16, 17, 18 for two different tumor bearing animals. Each mouse had two tumors but of different cell types. Different amounts of nanoparticles were absorbed by each of the two tumors.
- the mouse with MCF7 cells showed higher magnetic moments than the mouse with MDA-MB-231 tumors as expected due to the higher number of specific sites for HE 2/neu antibodies on the former.
- Fig. 15 is an illustration of the magnetic contour lines observed for 35 different measurement sites as described in Fig. 13. Analysis of these magnetic fields yielded the spatial positions of the tumors that agreed with the measured values of these positions; the SQUID results giving higher precision than the physical measurements of approximately 3 mm.
- 16 is an illustration of the time course of the measurements for the two mice and both tumors of each mouse. The uptake of the particles occurred rapidly with the signal near maximum obtained in the first hour. The nanoparticles remain in the tumors for at least 5 hours, the length of the experiments. Subsequent to these
- Fig. 17 are illustrations of the results of these measurements and show very good agreement with the in-vivo measurements on the live mouse.
- a magnetic moment was observed in the liver indicating that some phagocytosis had occurred and the particles were delivered to the liver for elimination.
- Subsequent histology of the tumors also showed significant attachment of the particles to cells in the tumor using Prussian blue staining to emphasize the iron in the magnetic nanoparticles.
- Fig.18 is an illustration of the 2-dimensional 95% confidence limit for the locations of the two tumors superimposed on the actual tumors of the mouse. An accuracy of spatial location of approximately +/- 3 mm is obtained in the x and y direction.
- Fig. 19 is a photo of the histology of tumors after extraction. Microscopic image of one MCF-7 tumor slice. Prussian Blue staining of cells reveals iron present in np attached to cells. Arrow points to cell covered with np.
- a sensitive magnetic field sensor system has been demonstrated for in-vivo early detection of breast cancer by detecting magnetic nanoparticles, conjugated to antibodies for breast cancer cell lines. More than 1 million nanoparticles attach to each cancer cell. Method is sensitive to ⁇ 100,000 cells at distances comparable to breast tumors. Standard x-ray mammography requires typically cell density of ten million cells. Measured moments are linear with cell number; i.e. measure of magnetic moment yields the number of cancer cells present. Very high contrast -nanoparticles not attached to cells are not observed. Phantom studies demonstrate multiple sources are localized accurately and number of cells per source determined.
- Mouse model was developed using multiple tumors of human breast cancer cell lines and in-vivo measurements made to determine the location and cancer cell count of these tumors subsequent to nanoparticle injections. Solutions of the inverse problem successfully locate tumors and number of cells. Histology confirms presence of np mouse tumors.
- ovarian cancer The etiology of ovarian cancer is not well understood and there is little evidence for risk factors suggesting preemptive screening.
- the normal screening test is pelvic examination if there are suspected symptoms, such as abdominal enlargement, and the results typically reveal advance stage of cancer. Routine screening of women presently is not done as there are no reliable screening tests.
- the great difficulty now with ovarian cancer is that by the time it is detected, it has metastasized from the ovary into other organs. For this reason, a hysterectomy is often performed along with the ovary removal. If the presence of ovarian cancer can be identified early and is contained in the ovary, the five year survival rate is 95%. However, only 29% are detected at this stage. If the disease has spread locally, this survival rate drops to 72% and if metastasized to distant locations, the rate of survival is 31%. Thus, development of early detection methods is imperative.
- Fig. 20 is an illustration of an ovarian cancer showing the growth of the tumor on the ovary. These tumors consist of cells with high numbers of receptors for the antibody CA-125 and can be targeted with magnetic nanoparticles labeled with this antibody.
- Fig. 21 is photograph of a full-size ovarian phantom placed under a SQUID sensor apparatus at a distance that would be typical of a patient subject. The phantom has a vial containing live ovarian cancer cells inserted into it.
- Magnetic nanoparticles labeled with the antibody CA-125 were inserted into this vial and because these antibodies are highly specific for these ovarian cancer cells, large numbers became attached to the cell surface. These magnetic nanoparticles were then detected by the SQUID sensor apparatus to provide sensitivity calibrations for in-vivo measurements for both animal and human in-vivo models.
- Fig. 22 The results of the sensitivity studies for live ovarian cells inserted into the phantom shown in Fig. 21 are illustrated in Fig. 22 for three different ovarian cancer cell lines; namely, tov-112D, Ov-90, and nihovcar-3.
- the plot shows the minimum number of cells that were detected by this apparatus for the three different cell lines as a function of distance from the sensor to the patient's ovaries.
- the cancer cell line ov-90 is known to be one of the most aggressive of the cancers and these results indicate that there are many receptors for CA-125 on the surface of the cell.
- the number of nanoparticles per cell can be estimated from these measurements and corresponds to 20,000 particles per cell for tov-112D, 3400 for ov-90, and 6700 for ovcar-3.
- FIG. 23 is an illustration of confirmation of antibody sites for these cells using flow cytometry.
- Figs. 23a and 23b show two of the four cell lines examined. The signal from cells only is shown and the isotype (using a non-specific binding molecule, Igg), the Her2/neu antibody, and CA-125 antibody are shown with increasing site number to the right on these plots. These figures show that the CA- 125 antibody has a large number of sites on these cells, with SK-OV-3 the largest of these two. The antibody Her2/neu is also specific to 30% of breast cancer cells.
- Measurement of the magnetic moment in the SQUID sensor apparatus as a function of time for magnetic moments from magnetic nanoparticles (from Ocean Nanotech) attached to ovarian human cancer tumors in the live mouse is shown in Fig. 24.
- the mouse had two ovarian tumors, one of SK-OV-3 and the other of NIH-OVCA 3.
- the magnetic nanoparticles were coated with a carboxyl biocompatible coating and were then conjugated to the CA-125 antibody. This antibody is specific to ovarian cancer cells in humans.
- the labeled magnetic nanoparticles were injected into the mouse tumors and the magnetic moments of the mouse measured at various times ranging from one minute to 300 minutes.
- the uptake of the particles occurred rapidly with the signal near maximum obtained in the first hour.
- the time course indicates that the nanoparticles remain in the tumors for a number of hours.
- the nanoparticles remained in the tumors for at least 5 hours, the length of the experiments.
- Different amounts of nanoparticles were absorbed by each of the two tumors.
- the mouse tumor with SK-OV-3 cells showed higher magnetic moments than the mouse with NIH-OVCAR-3 tumors, as expected due to the higher number of specific sites for CA-125 antibodies on the former.
- the nanoparticles gave no magnetic moment before injection and only yield a magnetic signal when attached to something such as the cells in the tumor.
- injections into sites other than the tumor do not yield a signal as the particles do not bind to normal cells.
- the liver begins to show signs of accumulation of these particles as they are phagocytised from the system.
- the mice were euthanized and the tumors and other organs removed and placed under the sensor apparatus to determine how much of the nanoparticle injections were in the tumors. These measurements agreed very well with the in-vivo measurements on the live mouse. Subsequent histology of the tumors showed significant attachment of the particles to cells in the tumor using Prussian blue staining to emphasize the iron in the magnetic nanoparticles.
- FIG. 25 A photograph of a mouse used to verify that the SQUID sensor method works in-vivo along with magnetic contour fields from this mouse are shown in Fig. 25.
- Human tumors are shown on the flanks of the mouse; these are the bumps above and to both sides of the tail in Fig. 25. These tumors were produced by injecting live human ovarian cancer cells into this severely-compromised- immune-deficient mouse and allowed to grow for several weeks until a 6 - 10 mm tumor was evident. The mouse was anesthetized through the tube over its mouth during all SQUID sensor experiments. Labeled magnetic nanoparticles were injected into the mouse at this stage either by tail, inter-peritoneal, or inter-tumoral injections.
- the mouse was placed under a sensor as shown in FIG. 1 and a magnetizing pulse was applied and the resulting magnetic moments of the injected particles was measured. As in the case of the live cancer cells, no moments were observed unless the particles had attached to cells within the tumors. In some cases both tumors were SK-OV-3 type cells and in other cases, two different cell lines were used to develop the tumors in the mice.
- the mouse placed on the stage shown in Fig. 5 could be moved to several positions under the sensor to obtain more spatial information.
- the mouse was typically placed at five stage positions under a 7-channel SQUID to obtain 35 spatial locations.
- the magnetic fields at all positions were then used in a code to solve the electromagnetic inverse problem using the Levenberg- Marquardt theorem to determine the location of all sources of magnetic particles in the mouse.
- This information was then compared to the known geometry of the mouse from photographs to determine the accuracy and sensitivity for locating cancer tumors in living animals.
- Fig. 25 shows the magnetic contour lines observed for 35 different measurements. Analysis of these magnetic fields yielded the spatial positions of the tumors that agreed with the measured values of these positions; the SQUID results giving higher precision than the physical measurements of approximately 3 mm.
- HL Hodgkin's lymphoma
- Another application where the present invention can have significant clinical impact is in the detection of persistent HL after therapy. If a patient experiencing a relapse undergoes high-dose radiation therapy, there is a good prognosis if the relapse is detected early. Patients who have a relapse will have a prognosis determined primarily by the duration of the first remission. The persistence of large fibrotic nodules, particularly in the mediastinum, after therapy leads to uncertainty in the determining whether persistent cancer is present and surgery of fibrotic nodules is fraught with difficulty to control bleeding problems and patient morbidity.
- the relaxometry method of the present invention can provide a quantitative estimation of the number of lymphoma cells present in organs affected by Hodgkin's disease, such as the thymus and spleen.
- the RS cells are giant cells derived from B-lymphocytes that contain millions of receptors for CD30 and CD15.
- Previous results with SQUID sensors targeting T-cell lymphocytes have shown that for smaller cells, approximately a million nanoparticles can be attached to each T-cell. Steric hindrance limits the number of nanoparticles attached to a normal lymphocyte but the much larger RS cells can have 25 to 50 times more bound nanoparticles.
- the amount of iron per nanoparticle is 4.4 x 10 "6 ng/np.
- each cell may have up to 10 ng of iron.
- One hundred RS cells accumulated in the spleen or thymus can contain a microgram of iron. Less than a microgram is adequate for SQUID detection, therefore a detectability of 100 RS cells is possible.
- the measured amplitude of the residual magnetization of the antibody-labeled nanoparticles in vivo can provide an important diagnostic tool in lymphoma cancer.
- the signal strength depends on the density of antigens on the tumor cell surfaces and thus the field strength produced by the nanoparticles is proportional to the number density of antigenic sites on lymphoma cells.
- the SQUID sensor is an ideal sensor system for Hodgkin's disease with large sensitivity for RS cells and in-vivo detection of the disease without biopsies and the ability to monitor the treatment of the disease during chemotherapy.
- Fig. 26 is a graph of a measurement of the magnetic moment in a SQUID sensor system as a function of time for incubation of attaching magnetic nanoparticles (from Ocean Nanotech) to lymphoma cell lines.
- the magnetic nanoparticles were coated with a carboxyl biocompatible coating and were then conjugated to the CD34 antibody.
- This antibody is specific to one type of lymphoma cells, namely, Acute Lymphomatic Leukemia in humans.
- the labeled magnetic nanoparticles were inserted into vials containing live cancer cells and the magnetic moments of the vial measured at various times ranging from one minute to 16 minutes. The zero time point is the magnetic moment of the vial of nanoparticles before adding to the cells.
- the lack of magnetic moment for the unmixed particles at time zero shows that unbound particles give no magnetic signal with this SQUID imaging method.
- the magnetic moments increase rapidly and saturate indicating that the cells have collected on their surfaces with the maximum number of nanoparticles possible in one to two minutes.
- the top curve is for the lymphoma cancer cell line U937 that is known to be very specific for the CD34 antibody and the large magnitude of the magnetic signal verifies this.
- the lower curve is for the same cell line but a non-specific marker, BSA, and shows substantially smaller magnetic moments after incubation. The presence of a magnetic moment for the BSA is indicative of some phagocytosis of these cells where the nanoparticles enter the cells.
- U937 is a lymphoma of the T lymphocyte cells and S is a lymphoma of the B lymphocyte cells. Since one of the principle purposes of lymphocyte cells is to take up particles that do not belong, this amount of non-specificity is expected. These results demonstrate the specificity of the antibody for the target cancer cells and verify that only bound particles give magnetic moments. This result is not true for other methods such as MRI which sees all particles, bound or unbound.
- Samples of RS cells were obtained from the Tissue Bank facility at the University of New Mexico, a nationally recognized institution for cell banking and quantity of specimens. The efficiency of the SQUID sensor system for detecting RS cells was compared to the number of RS cells in a sample determined by manual hematocytometer counts. These isolated RS cells were labeled with nanoparticles specificity bound to CD15 and CD30 during the isolation procedure. Calibration of sensitivity was performed by serially dilution over a range of 1 in 10 to 1 in 100,000 cells. Ranges of nanoparticle density on malignant cells exceed 107 nanoparticles/cell. The site density of CD15 is determined using a flow cytometry technique that quantifies receptors/cell. The number of CD15 and CD30 sites/cell was confirmed using a quantitative immunofluorescence staining technique.
- Fig. 27 is an illustration of the results of the flow cytometric measurements of RS cells from the lymphatic system in determining the number of sites available for nanoparticles and detection by the SQUID sensors.
- Fig. 27A is a photograph showing the morphologic appearance of RS cells isolated from a lymph node specimen.
- Fig. 27B shows the flow cytometric analysis of a bone marrow sample where (Bl) is before and (B2) after performing an enrichment procedure to enhance the frequency of RS cells in a sample for flow cytometry.
- Normally RS cells occur at a frequency of 1 in 104 or 105 of normal lymphocyte cells and must be enhanced before using CD15 and CD30 staining by flow cytometry in order to be detected.
- the SQUID sensor system detects all of the RS cells in- vivo and does not require sampling so enhancement is not necessary, as is required in the flow cytometry determinations.
- the lymph nodes are one of the primary sites where RS cells accumulate, aside from the thymus gland.
- Fig. 28 is a histology slice from a patient with Hodgkin's Disease.
- the RS cells have been stained with immunoperoxidase staining.
- the antibody CD15 is shown on the right and the antibody CD30 on the left.
- the surrounding cells are non-malignant cells in the lymph node.
- the SQUID sensor can detect several hundred of these labeled RS cells in a lymph node.
- Prostate cancer has a high mortality rate due to the lack of early detection with standard screening technologies. The number of cases for 2009 in the US was 192,280 with 27,360 deaths. Prostate cancer accounts for 9% of male deaths and there is a 1 in 6 lifetime probability for developing prostate cancer. The disease is normally undetected until it has caused an enlargement of the prostate, urinary problems, or has spread to other organs. Asymptomatic detection of the disease is normally done by a digital examination, an elevated PSA test result, or a biopsy. The PSA test is now considered unreliable causing many unnecessary biopsies with accompanying dangers of infection. The digital examination is also highly subjective. Testing for prostate cancer is very controversial. The cost of PSA tests in the US alone exceed $3 billion and a recent study reported in the New England Journal of Medicine found that current screening methods do not reduce the death rate in men over 55 years old. The present invention can detect this cancer before it has metastasized.
- An exemplary method to detect prostate cancer in a tissue comprises placing the patient on a measurement stage of a superconducting quantum interference device sensor apparatus; injecting a plurality of antibody-labeled magnetic nanoparticles into the patient for specific binding to the tissue in the patient; applying a uniform magnetizing pulse field to magnetize the nanoparticles injected into the patient; and detecting the residual magnetic field of the magnetized nanoparticles thereby providing an image of the nanoparticles bound to the tissue of the patient.
- the tissue can comprise prostate tissue and the antibody-labeled magnetic nanoparticles can specifically bind to antigens of prostate cancer cells.
- the antibody-labeled magnetic nanoparticle can comprise a magnetic core coated with a biocompatible coating to which is attached specific antibodies.
- the magnetic core can comprise a ferromagnetic material, such as iron oxide.
- the biocompatible coating can comprise Dextran, carboxyl, or amine.
- the specific antibody can be PSMA antibody.
- the prostate-specific membrane antigen is a transmembrane glycoprotein that is highly expressed by most prostate cancers. It is also referred to as mAb 7E11. It is expressed on the surface of the tumor vascular endothelium of solid carcinomas but not on normal prostate cells.
- the amount of PSMA observed in prostate cancer follows the severity or grade of the tumor. Flow cytometry has shown that there are large numbers of receptor sites for this antibody on several cell lines of prostate cancer including LNCaP and PC-3, whereas a PSMA negative cell line, DU-145 indicates no expression. Results of attaching magnetic nanoparticles to these positive cell lines demonstrate one million or more nanoparticles per cell.
- the SQUID sensor method can provide a quantitative estimation of microvascular structure in tumors leading to a new surrogate for vessel formation (angiogenesis) and individual tumor gradation. It has been shown in a study of tumor microvascular characterization in an experimental prostate cancer model using nanoparticles that tumor growth and aggressiveness/grade have a direct relationship to tumor neovascularization. Other studies estimate the concentration of magnetic particles in a tumor to be about 2.3 mg of nanoparticles per gram of tissue. This concentration is regularly achieved in the tumors of human liver cancer patients receiving treatment via intrahepatic arterially administered radioactive microspheres; the nanoparticles tend to concentrate in the vascular growth ring of a tumor. Less than a nanogram is adequate for SQUID detection.
- the measured amplitude of the residual magnetization of the antibody-labeled nanoparticles in vivo can provide an important diagnostic tool in prostate cancer.
- the signal strength depends on the density of antigens on the tumor cell surfaces and thus the field strength produced by the nanoparticles is proportional to the number density of antigenic sites on prostate tumor cells.
- particle number and density provides the amplitude of the detected magnetic field. This information can then be used in planning in vivo, as well as for assisting in the choice of nanoparticles to be used.
- Brain cancer is particularly deadly and occurs in a number of forms. Cancer involving the glial cells is the most prevalent form and also the most aggressive brain tumor in humans. Various glial cells may be involved causing cancer of the type oligodendroglioma (involving the oligodendrocytes), astrocytoma (involving the astrocytes) and glioblastoma. The latter is the most frequently occurring of the brain cancers. These types of cancer normally results in death within a very short period of time. Gliablastoma cells can be targeted by markers such as EGFR, 81C6, and PTN antibodies that may be used to image this type of cancer. Mouse models and brain cancer cell lines, such as U-251, are available for testing before human applications.
- nanoparticles with markers attached. This barrier is somewhat opened in the vascular system associated with malignant tumors but still remains an impediment.
- the use of nanoparticles coated with lipophilic surfaces and then conjugated to antibodies or peptides increases the ability to cross the barrier.
- the nanoparticle with markers can be encapsulated in a polymer coating with a liposome surface of in a micelle is another approach and releasing the conjugated nanoparticles from the polymer once inside of the brain using a slight application of a heating F or ultrasound pulse.
- An exemplary method to detect brain cancer comprises placing the patient on a measurement stage of a superconducting quantum interference device sensor apparatus; injecting a plurality of antibody-labeled magnetic nanoparticles into the patient for specific binding to the brain tumor in the patient; applying a uniform magnetizing pulse field to magnetize the nanoparticles injected into the patient; and detecting the residual magnetic field of the magnetized nanoparticles thereby providing an image of the nanoparticles bound to the tissue of the patient.
- the target is a brain tumor and the antibody-labeled magnetic nanoparticles can specifically bind to antigens of brain cancer cells.
- the antibody-labeled magnetic nanoparticle can comprise a magnetic core coated with a biocompatible coating to which is attached specific antibodies.
- the magnetic core can comprise a ferromagnetic material, such as iron oxide.
- the biocompatible coating can comprise Dextran, carboxyl, or amine.
- the specific antibody can be EGFR or similar antibody.
- Angiogenesis EGFR has several forms and is a version of the epidermal growth factor receptor (EGFR) that is overexpressed by several types of cancer cells including glioblastoma cells and not normal cells.
- EGFR epidermal growth factor receptor
- It can be conjugated with magnetic nanoparticles suitable for magnetic relaxometry detection and injected into the body.
- These magnetic nanoparticles can comprise a coating, such as polyethylene glycol (PEG), that will increase the efficacy of the targeted nanoparticles for penetrating the blood brain barrier.
- PEG polyethylene glycol
- the magnetic nanoparticles with markers attached can be contained within polymer coatings that are able to penetrate through the blood brain barrier and then released upon the application of a small RF heating pulse or the use of ultrasound.
- Results of attaching these angiogenesis peptides to magnetic nanoparticles and attaching these to cells are comparable to the use of other antibody results from ovarian and breast cancer regarding nanoparticles per cell and depths of tumors in the body.
- Biomagnetic detection methods using systems such as SQUID sensors will have the same sensitivity for brain cancer as ovarian cancer (described in one or more of the related applications incorporated by reference above). Results of studies on breast and ovarian cancer can thus be directly applied to brain cancer detection and localization.
- CA19-9 is one example of a marker that is elevated in this cancer but is not very sensitive (77%) and non-specific (87%) .
- Combinations of markers have been suggested by the M.D. Anderson Cancer Center and these are being tested for screening of pancreatic cancer.
- These markers are micro NAs and include miR-21, MiR-210, miR-155 and miR-196a. However, this combination also only achieves a low sensitivity (64%) but a higher specificity (89%) than the CA19-9.
- a number of antibodies have been identified against certain cell lines of human pancreatic cancer, for example the FG cell line and these include S3-15, S3-23, S3-41, S3-60, S3-110, and S3-53.
- uPAR urokinase plasminogen activator receptor
- MRI Magnetic Contrast Enhanced
- MRI imaging of tumors often uses magnetic nanoparticles as contrast agents as mentioned above and is an accepted protocol providing standards for the injection of such nanoparticles.
- Intravascular MRI contrast agents at a dose of 2mg/kg of nanoparticle weight have been used to detect metastatic lesions.
- the use of MRI in pancreatic cancer is severely limited.
- the present invention can provide a quantitative estimation of microvascular structure in tumors leading to a new surrogate for vessel formation (angiogenesis) and individual tumor gradation. It has been shown in results in a study of tumor microvascular characterization in an experimental pancreatic cancer model using nanoparticles that tumor growth and
- Nanograms are adequate for detection by the present invention.
- the measured amplitude of the residual magnetization of the antibody-labeled nanoparticles in vivo can provide an important diagnostic tool in pancreatic cancer.
- the signal strength depends on the density of antigens on the tumor cell surfaces and thus the field strength produced by the nanoparticles is proportional to the number density of antigenic sites on pancreatic tumor cells.
- Particle number and density can be determined to provide the amplitude of the detected magnetic field. This information can be used in planning in vivo detection, as well as for assisting in the choice of nanoparticles to be used.
- pancreatic cancer cell lines include FG or MIA PaCa-2 that are known to be specific for the uPA antibody.
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Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8447379B2 (en) | 2006-11-16 | 2013-05-21 | Senior Scientific, LLC | Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof |
WO2013150926A1 (en) * | 2012-04-06 | 2013-10-10 | 株式会社日立製作所 | Magnetic field measurement device |
US8999650B2 (en) | 2004-03-01 | 2015-04-07 | Senior Scientific Llc | Magnetic needle biopsy |
WO2015089268A1 (en) | 2013-12-11 | 2015-06-18 | University Of Massachusetts | Compositions and methods for treating disease using salmonella t3ss effector protein (sipa) |
US9095270B2 (en) | 2009-11-06 | 2015-08-04 | Senior Scientific Llc | Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof |
Families Citing this family (13)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20160206226A1 (en) * | 2009-11-06 | 2016-07-21 | Senior Scientific Llc | Detection, Measurement, And Imaging Of Cells Using Cellular Internalization of Nanoparticles |
US8593141B1 (en) | 2009-11-24 | 2013-11-26 | Hypres, Inc. | Magnetic resonance system and method employing a digital squid |
US8970217B1 (en) | 2010-04-14 | 2015-03-03 | Hypres, Inc. | System and method for noise reduction in magnetic resonance imaging |
US20150369887A1 (en) * | 2014-06-19 | 2015-12-24 | Senior Scientific Llc | Methods and apparatuses related to instrumentation for magnetic relaxometry measurements |
US20170056683A1 (en) * | 2015-04-27 | 2017-03-02 | Ariel-University Research And Development Company Ltd. | Method and device using high-intensity millimeter waves |
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DE102017209373A1 (en) * | 2017-06-02 | 2018-12-06 | Bruker Biospin Mri Gmbh | Fast method for determining the position of a ferromagnetic particle or a bundle of ferromagnetic particles with MRI systems |
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CN113692302A (en) | 2019-02-07 | 2021-11-23 | V·K·沙玛 | System and method for treating cancer cells with alternating polarity magnetic fields |
US11344740B2 (en) | 2019-02-07 | 2022-05-31 | Asha Medical, Inc. | System and methods for treating cancer cells with alternating polarity magnetic fields |
US11027143B2 (en) | 2020-02-06 | 2021-06-08 | Vivek K. Sharma | System and methods for treating cancer cells with alternating polarity magnetic fields |
US11136543B1 (en) | 2020-02-11 | 2021-10-05 | Edward R. Flynn | Magnetic cell incubation device |
CN114645014B (en) * | 2021-12-07 | 2024-04-02 | 深圳先进技术研究院 | Immune cell modification method, immune cell robot and immune cell modification system |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4442404A (en) * | 1978-12-19 | 1984-04-10 | Bergmann Wilfried H | Method and means for the noninvasive, local, in-vivo examination of endogeneous tissue, organs, bones, nerves and circulating blood on account of spin-echo techniques |
US6470220B1 (en) | 1999-03-29 | 2002-10-22 | The Regents Of The University Of California | Diagnosis and treatment of cancers using in vivo magnetic domains |
US20020177769A1 (en) | 2001-04-23 | 2002-11-28 | The Regents Of The University Of California | Method and apparatus for locating cells in the body by measuring magnetic moments |
US20090156659A1 (en) * | 2004-07-27 | 2009-06-18 | Butters John T | System and method for collecting, storing, processing, transmitting and presenting very low amplitude signals |
US20090243610A1 (en) * | 2008-03-26 | 2009-10-01 | Canon Kabushiki Kaisha | Atomic magnetometer and magnetic force measuring method |
Family Cites Families (85)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3741198A (en) | 1971-10-12 | 1973-06-26 | Univ Temple | Radiological diagnostic method |
US4018886A (en) | 1975-07-01 | 1977-04-19 | General Electric Company | Diagnostic method and device employing protein-coated magnetic particles |
FR2351646A1 (en) | 1976-05-19 | 1977-12-16 | Nogier Paul | IMPROVEMENTS IN ACUPUNCTURE METHODS AND EQUIPMENT |
JPS5373892A (en) | 1976-12-11 | 1978-06-30 | Kenkichi Tsukamoto | Improved needle and attached ampule |
US4346715A (en) | 1978-07-12 | 1982-08-31 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Hyperthermia heating apparatus |
US4574782A (en) | 1981-11-16 | 1986-03-11 | Corning Glass Works | Radio frequency-induced hyperthermia for tumor therapy |
DE3247585A1 (en) * | 1982-12-22 | 1984-06-28 | Siemens AG, 1000 Berlin und 8000 München | MULTI-CHANNEL DEVICE FOR MEASURING DIFFERENT FIELD SOURCES OF LOW MAGNETIC FIELDS |
EP0330801A1 (en) | 1983-02-08 | 1989-09-06 | Schering Aktiengesellschaft | Ferromagnetic, diamagnetic or paramagnetic particles useful in the diagnosis and treatment of disease |
US4735796A (en) | 1983-12-08 | 1988-04-05 | Gordon Robert T | Ferromagnetic, diamagnetic or paramagnetic particles useful in the diagnosis and treatment of disease |
US4590922A (en) | 1983-08-19 | 1986-05-27 | Gordon Robert T | Use of ferromagnetic, paramagnetic and diamagnetic particles in the treatment of infectious diseases |
US4829984A (en) | 1983-12-15 | 1989-05-16 | Gordon Robert T | Method for the improvement of transplantation techniques and for the preservation of tissue |
US4675286A (en) | 1985-01-28 | 1987-06-23 | Aspen Diagnostics, Inc. | Fetal cell separation and testing |
US4950221A (en) | 1986-07-18 | 1990-08-21 | Gordon Robert T | Process for affecting molecules in tissue |
US5231000A (en) | 1987-10-08 | 1993-07-27 | The Mclean Hospital | Antibodies to A4 amyloid peptide |
JPH0284933A (en) * | 1988-09-21 | 1990-03-26 | Matsushita Electric Ind Co Ltd | Magnetic diagnostic device |
US5203782A (en) | 1990-04-02 | 1993-04-20 | Gudov Vasily F | Method and apparatus for treating malignant tumors by local hyperpyrexia |
US5067952A (en) | 1990-04-02 | 1991-11-26 | Gudov Vasily F | Method and apparatus for treating malignant tumors by local hyperpyrexia |
GB9007408D0 (en) * | 1990-04-02 | 1990-05-30 | Nycomed As | Compositions |
JPH045590A (en) * | 1990-04-23 | 1992-01-09 | Seiko Instr Inc | Multichannel plane type gradiometer |
US5408178A (en) * | 1991-05-17 | 1995-04-18 | Vanderbilt University | Apparatus and method for imaging the structure of diamagnetic and paramagnetic objects |
GB9120508D0 (en) | 1991-09-26 | 1991-11-06 | Nycomed As | Diagnostic agents |
US5486161A (en) | 1993-02-02 | 1996-01-23 | Zomed International | Medical probe device and method |
US6005916A (en) | 1992-10-14 | 1999-12-21 | Techniscan, Inc. | Apparatus and method for imaging with wavefields using inverse scattering techniques |
US5409813A (en) | 1993-09-30 | 1995-04-25 | Systemix, Inc. | Method for mammalian cell separation from a mixture of cell populations |
JP2690678B2 (en) * | 1993-11-08 | 1997-12-10 | 大阪瓦斯株式会社 | Approximate model display device |
US6958062B1 (en) | 1993-11-08 | 2005-10-25 | Rita Medical Systems, Inc. | Multiple antenna ablation apparatus and method |
US5599345A (en) | 1993-11-08 | 1997-02-04 | Zomed International, Inc. | RF treatment apparatus |
DE4445700A1 (en) * | 1994-12-21 | 1996-06-27 | Forschungszentrum Juelich Gmbh | Gradiometer |
DE19503664C2 (en) | 1995-01-27 | 1998-04-02 | Schering Ag | Magnetorelaxometric detection of analytes |
US5782764A (en) | 1995-11-07 | 1998-07-21 | Iti Medical Technologies, Inc. | Fiber composite invasive medical instruments and methods for use in interventional imaging procedures |
US5715837A (en) | 1996-08-29 | 1998-02-10 | Light Sciences Limited Partnership | Transcutaneous electromagnetic energy transfer |
US6058323A (en) | 1996-11-05 | 2000-05-02 | Lemelson; Jerome | System and method for treating select tissue in a living being |
US5921244A (en) | 1997-06-11 | 1999-07-13 | Light Sciences Limited Partnership | Internal magnetic device to enhance drug therapy |
WO1999023934A2 (en) | 1997-11-12 | 1999-05-20 | Stereotaxis, Inc. | Articulated magnetic guidance systems and devices and methods for magnetically-assisted surgery |
US6203487B1 (en) | 1997-12-31 | 2001-03-20 | Thomas Jefferson University | Use of magnetic particles in the focal delivery of cells |
US6697660B1 (en) * | 1998-01-23 | 2004-02-24 | Ctf Systems, Inc. | Method for functional brain imaging from magnetoencephalographic data by estimation of source signal-to-noise ratio |
WO1999067284A2 (en) | 1998-06-20 | 1999-12-29 | Washington University | Membrane-permeant peptide complexes for medical imaging, diagnostics, and pharmaceutical therapy |
US7534866B2 (en) * | 2005-10-19 | 2009-05-19 | Ibc Pharmaceuticals, Inc. | Methods and compositions for generating bioactive assemblies of increased complexity and uses |
SE9903185D0 (en) | 1999-09-08 | 1999-09-08 | Europ I Of Science Ab | Therapeutic method and device based on magnetism |
AU2001249795A1 (en) | 2000-04-04 | 2001-10-15 | Mayo Foundation For Medical Education And Research | Methods for detecting plaques in vivo |
US20020123079A1 (en) | 2000-10-20 | 2002-09-05 | Qi Chen | Process for detecting or quantifying a biological rreaction using superparamagnetic label |
US6488668B1 (en) | 2000-11-16 | 2002-12-03 | Ideal Instruments, Inc. | Detectable heavy duty needle |
ATE365565T1 (en) | 2001-03-08 | 2007-07-15 | Ct Angewandte Nanotech Can | PARAMAGNETIC NANOPARTICLES |
WO2002094191A2 (en) | 2001-05-23 | 2002-11-28 | New York University | Detection of alzheimer's amyloid by magnetic resonance imaging |
US7053109B2 (en) | 2001-07-10 | 2006-05-30 | Pharmacia & Upjohn Company | Aminediols for the treatment of Alzheimer's disease |
US7731648B2 (en) | 2001-07-25 | 2010-06-08 | Aduro Biotech | Magnetic nanoscale particle compositions, and therapeutic methods related thereto |
US7074175B2 (en) | 2001-07-25 | 2006-07-11 | Erik Schroeder Handy | Thermotherapy via targeted delivery of nanoscale magnetic particles |
US6997863B2 (en) * | 2001-07-25 | 2006-02-14 | Triton Biosystems, Inc. | Thermotherapy via targeted delivery of nanoscale magnetic particles |
US7048890B2 (en) * | 2001-12-21 | 2006-05-23 | Koninklijke Philips Electronics N.V. | Sensor and method for measuring the areal density of magnetic nanoparticles on a micro-array |
US7081123B2 (en) | 2002-06-18 | 2006-07-25 | Musculoskeletal Transplant Foundation | Bone marrow aspiration instrument |
AU2003303954A1 (en) | 2002-10-25 | 2004-10-11 | Emory University | Multifunctional magnetic nanoparticle probes for intracellular molecular imaging and monitoring |
JP2004157072A (en) | 2002-11-08 | 2004-06-03 | Japan Science & Technology Agency | Highly-sensitive magnetic marker used for immunoreaction measurement |
FR2848850B1 (en) | 2002-12-20 | 2005-06-24 | Guerbet Sa | NOVEL MAGNETIC PARTICLES COMPOSITIONS COVERED WITH GEM-BISPHOSPHONATE DERIVATIVES. |
DE10331439B3 (en) * | 2003-07-10 | 2005-02-03 | Micromod Partikeltechnologie Gmbh | Magnetic nanoparticles with improved magnetic properties |
US7396589B2 (en) | 2003-07-31 | 2008-07-08 | Industrial Technology Research Institute | Core-shell magnetic nanoparticles comprising an inner-transition element |
US7662362B2 (en) | 2003-09-05 | 2010-02-16 | The Ohio State University Research Foundation | Nanoparticulate probe for in vivo monitoring of tissue oxygenation |
US20050090732A1 (en) | 2003-10-28 | 2005-04-28 | Triton Biosystems, Inc. | Therapy via targeted delivery of nanoscale particles |
US7906345B2 (en) | 2003-11-12 | 2011-03-15 | The Board Of Trustees Of The Leland Stanford Junior University | Magnetic nanoparticles, magnetic detector arrays, and methods for their use in detecting biological molecules |
GB0329310D0 (en) | 2003-12-18 | 2004-01-21 | Univ Keele | Method |
US8118754B1 (en) | 2007-11-15 | 2012-02-21 | Flynn Edward R | Magnetic needle biopsy |
US7745001B2 (en) | 2004-03-23 | 2010-06-29 | University Of New Orleans Research And Technology Foundation, Inc. | Synthesis of nanoassemblies containing luminescent quantum dots and magnetic nanoparticles |
US20060018835A1 (en) | 2004-04-02 | 2006-01-26 | General Electric Company | Nanoparticles with inorganic core and methods of using them |
US7842281B2 (en) | 2004-05-10 | 2010-11-30 | The Florida State University Research Foundation | Magnetic particle composition for therapeutic hyperthermia |
US20060140871A1 (en) | 2004-11-30 | 2006-06-29 | Sillerud Laurel O | Magnetic resonance imaging of prostate cancer |
US20080093219A1 (en) | 2005-03-15 | 2008-04-24 | Tufts University | Magnetic Protein Nanosensors and Methods of Use |
US8456157B2 (en) | 2005-07-27 | 2013-06-04 | University Of Houston | Nanomagnetic detector array for biomolecular recognition |
EP1912564A2 (en) | 2005-08-09 | 2008-04-23 | Board of Supervisors of Louisiana State University and Agricultural and Mechanical College | In vivo imaging and therapy with magnetic nanoparticle conjugates |
US20070197900A1 (en) | 2005-11-22 | 2007-08-23 | Vanderbilt University | Magnetic flow cytometer with SQUID microscopy |
US7573264B2 (en) * | 2005-11-28 | 2009-08-11 | The Regents Of The University Of California | Atomic magnetic gradiometer for room temperature high sensitivity magnetic field detection |
US20070140974A1 (en) | 2005-12-15 | 2007-06-21 | General Electric Company | Targeted nanoparticles for magnetic resonance imaging |
TWI293113B (en) | 2005-12-23 | 2008-02-01 | Ind Tech Res Inst | Magnetic nanoparticles with fluorescent and specific targeting functions |
US20100021391A1 (en) | 2006-07-14 | 2010-01-28 | Montana State University | Novel nanoparticles for biofilm targeting |
US8339135B2 (en) | 2006-08-21 | 2012-12-25 | Stc.Unm | Biological detector and method |
JP2010508022A (en) | 2006-10-30 | 2010-03-18 | サザン リサーチ インスティチュート | Targeting NBS1-ATM to sensitize cancer cells to radiation therapy and chemotherapy |
AU2007352361A1 (en) | 2006-11-14 | 2008-11-06 | The Cleveland Clinic Foundation | Magnetic cell separation |
US8447379B2 (en) | 2006-11-16 | 2013-05-21 | Senior Scientific, LLC | Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof |
WO2011053435A1 (en) | 2009-10-05 | 2011-05-05 | Scientific Nanomedicine, Inc. | Cell detection using targeted nanoparticles and magnetic properties thereof |
WO2008140831A2 (en) | 2007-01-18 | 2008-11-20 | Trustees Of Dartmouth College | Iron/iron oxide nanoparticle and use thereof |
CA2693678C (en) | 2007-07-10 | 2017-02-14 | Carnegie Mellon University | Compositions and methods for producing cellular labels for nuclear magnetic resonance techniques |
US8179135B2 (en) | 2008-01-28 | 2012-05-15 | California Institute Of Technology | Low field electron paramagnetic resonance imaging with SQUID detection |
US8722017B2 (en) | 2008-07-10 | 2014-05-13 | The Board Of Trustees Of The Leland Stanford Junior University | Fluorescent magnetic nanoprobes, methods of making, and methods of use |
US9167983B2 (en) * | 2008-08-15 | 2015-10-27 | The University Of Houston System | Imaging method for obtaining spatial distribution of nanoparticles in the body |
CA2780148C (en) | 2009-11-06 | 2017-02-28 | Scientific Nanomedicine, Inc. | Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof |
CN102893172A (en) | 2010-03-16 | 2013-01-23 | 纳米医学科学公司 | Nonsurgical determination of organ transplant condition |
SG10201503516VA (en) | 2010-05-12 | 2015-06-29 | Pelican Imaging Corp | Architectures for imager arrays and array cameras |
-
2010
- 2010-11-05 CA CA2780148A patent/CA2780148C/en active Active
- 2010-11-05 WO PCT/US2010/055729 patent/WO2011057146A1/en active Application Filing
- 2010-11-05 JP JP2012538052A patent/JP5805651B2/en active Active
- 2010-11-05 KR KR1020127014490A patent/KR20120087165A/en not_active Application Discontinuation
- 2010-11-05 CN CN201080059742.1A patent/CN102695473B/en active Active
- 2010-11-05 US US13/503,674 patent/US9095270B2/en active Active
- 2010-11-05 AU AU2010315007A patent/AU2010315007B2/en active Active
- 2010-11-05 EP EP10829197.2A patent/EP2496175A4/en not_active Withdrawn
-
2012
- 2012-05-03 IL IL219566A patent/IL219566A/en active IP Right Grant
-
2015
- 2015-05-04 US US14/702,977 patent/US20150250403A1/en not_active Abandoned
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4442404A (en) * | 1978-12-19 | 1984-04-10 | Bergmann Wilfried H | Method and means for the noninvasive, local, in-vivo examination of endogeneous tissue, organs, bones, nerves and circulating blood on account of spin-echo techniques |
US6470220B1 (en) | 1999-03-29 | 2002-10-22 | The Regents Of The University Of California | Diagnosis and treatment of cancers using in vivo magnetic domains |
US20020177769A1 (en) | 2001-04-23 | 2002-11-28 | The Regents Of The University Of California | Method and apparatus for locating cells in the body by measuring magnetic moments |
US20090156659A1 (en) * | 2004-07-27 | 2009-06-18 | Butters John T | System and method for collecting, storing, processing, transmitting and presenting very low amplitude signals |
US20090243610A1 (en) * | 2008-03-26 | 2009-10-01 | Canon Kabushiki Kaisha | Atomic magnetometer and magnetic force measuring method |
Non-Patent Citations (4)
Title |
---|
FLYNN ET AL., JOURNAL OF MAGNETISM AND MAGNETIC MATERIALS, vol. 311, 2007, pages 429 - 435 |
JIA ET AL., JOURNAL OF MAGNETISM AND MAGNETIC MATERIALS, vol. 320, 2008, pages 1472 - 1478 |
See also references of EP2496175A4 |
TAMANAHA ET AL., BIOSENSORS AND BIOELECTRONICS, vol. 24, 2008, pages 1 - 13 |
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Publication number | Priority date | Publication date | Assignee | Title |
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US8999650B2 (en) | 2004-03-01 | 2015-04-07 | Senior Scientific Llc | Magnetic needle biopsy |
US8447379B2 (en) | 2006-11-16 | 2013-05-21 | Senior Scientific, LLC | Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof |
US9095270B2 (en) | 2009-11-06 | 2015-08-04 | Senior Scientific Llc | Detection, measurement, and imaging of cells such as cancer and other biologic substances using targeted nanoparticles and magnetic properties thereof |
WO2013150926A1 (en) * | 2012-04-06 | 2013-10-10 | 株式会社日立製作所 | Magnetic field measurement device |
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Also Published As
Publication number | Publication date |
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EP2496175A4 (en) | 2014-08-06 |
KR20120087165A (en) | 2012-08-06 |
RU2012120429A (en) | 2014-03-20 |
EP2496175A1 (en) | 2012-09-12 |
CA2780148C (en) | 2017-02-28 |
US20130121927A1 (en) | 2013-05-16 |
CA2780148A1 (en) | 2011-05-12 |
US9095270B2 (en) | 2015-08-04 |
US20150250403A1 (en) | 2015-09-10 |
IL219566A0 (en) | 2012-06-28 |
AU2010315007B2 (en) | 2015-05-21 |
JP2013509965A (en) | 2013-03-21 |
CN102695473A (en) | 2012-09-26 |
JP5805651B2 (en) | 2015-11-04 |
CN102695473B (en) | 2015-09-23 |
AU2010315007A1 (en) | 2012-05-31 |
IL219566A (en) | 2015-04-30 |
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