Lightweight portable MRI assembly

Abstract

A portable assembly for an MRI imaging system has independently adjustable modules of a scanner bore having electromagnets positioned along its inner wall, each electromagnet including a coil assembly. An independent power supply, controlled by a controller, connected to each of the electromagnets includes piezoelectric material and generates pulses of electric current (at a specified frequency and for a specified duration) and an electromagnetic field. Detectors positioned along the inner wall are configured to detect a reflected signal while the tissue of the subject is under an influence of the electromagnetic field, and to transmit the reflected signal for a remote computer system to generate an image, an analysis and / or a diagnosis. Cooling water inside coils may include nanoparticles, be hydrogenated and / or induce a water vortex. The electromagnets may be superconductive at a relatively high temperature and may utilize AI-calibrated frequencies. Images generated may be 3-dimensional and converted to 2-dimensional.

Description

[0001] SH-MICH-008-PCT

[0002] LIGHTWEIGHT PORTABLE MRI ASSEMBLY

[0003] Field of the Invention

[0004] The embodiments described herein generally relate to an assembly for a portable MRI imaging system or machine, and more particularly, in some embodiments, to an assembly for MRI imaging systems that utilizes the emission of brief pulses of electricity for its electromagnets. Background

[0005] There are two types of stationary MRI imaging systems - those that use permanent magnets and those that use superconductive magnets. As of 2023 about 70% of MRI imaging systems installed worldwide use superconducting magnets. These machines weigh 4,500 Kgs (1.5 T) or 7.500 Kgs (3.0 T). Other MRI imaging machines use permanent magnets, which weigh up to 16,000 Kgs. Both types of MRI imaging systems expend a lot of energy and generate a lot of heat. They therefore require built-in cooling systems involving many heavy condensers.

[0006] Besides the weight, other drawbacks of MRI imaging systems include their much higher cost, and patient discomfort with the procedure. The electromagnets of an MRI machine are also very powerful and necessitate shielding the whole room in which the MRI scanning occurs.

[0007] MRI imaging systems are also not as accessible as they could be. An MRI scan can only be done in a hospital and typically requires scheduling well in advance.

[0008] There is a portable MRI imaging system for the head produced by Hyperfine®, Inc. called the Swoop® system. The company states that it weighs about 635 Kgs (1,400 pounds). It is not designed to be used outside of a hospital, although it claims to be wheelable to the patient within the hospital. It utilizes a permanent magnet having a magnetic field strength of 64 mT (milli Tesla). Its claimed operating temperature range is 15 to 30 degrees Celsius. However, the quality of its brain imaging is believed by Applicant to not be of high quality because the use of an outside magnetic field strength of 64 milli Tesla means that the flip angle of the protons (in the tissue of the patient) exhibiting precession is low. As a result, the MRI signals emitted from the brain tissue using the Hyperfine® system are of low intensity, and have a low signal to noise ratio. The resulting brain imaging has low contrast and spatial resolution. The low contrast and spatial resolution of the brain images is further exacerbated by the absence of a cooling system, which elevates the noise signals and lowers the level of beneficial MRI signals. SH-MICH-008-PCT

[0009] SUMMARY OF THE EMBODIMENTS

[0010] One embodiment is a portable assembly for an MRI imaging system, the assembly comprising a scanner bore having an inner wall; electromagnets positioned along the inner wall, each electromagnet comprising a metallic core that generates an electromagnetic field, the core surrounded by a coil assembly configured to emit a radio frequency (RF) signal to the subject; a power supply connected to each of the electromagnets, the power supply comprising piezoelectric material and an actuator, the power supply configured to generate pulses of electric current and the electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject inside the scanner bore during a hiatus between the pulses, and to transmit the reflected signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis, wherein the generated pulses are of a duration of a second or less.

[0011] In some embodiments, the power supply is configured to generate 3 to 300 pulses per second.

[0012] In some embodiments, the power supply is configured to generate 30 to 6000 pulses per second.

[0013] In some embodiments, the power supply is configured to generate 300 or fewer pulses per second.

[0014] In some embodiments, the power supply is configured to produce a current of 10 to 300 amperes.

[0015] In some embodiments, the power supply is configured to produce a voltage of 0.1 to 10 kilovolts.

[0016] In some embodiments, the power supply is configured to generate 1-3000 kilowatts.

[0017] In some embodiments, a frequency of the coil assembly is from 100 KHz to 10 MHz.

[0018] In some embodiments, the duration of each of the generated pulses is one third of a second or less.

[0019] In some embodiments, the duration of each of the generated pulses is 3.3 milliseconds to 333 milliseconds.

[0020] In some embodiments, the scanner bore is radially or circumferentially adjustable. SH-MICH-008-PCT

[0021] In some embodiments, the portable assembly further comprises each of a series of pneumatic actuators situated between the coil assemblies of the electromagnetics for adjustment of a diameter of the scanner bore. In some embodiments, the portable assembly further comprises a central electromechanical actuator from which multiple connecting levers extend to each of the coil assemblies for precise adjustment of a diameter or circumference of the scanner bore.

[0022] In some embodiments, a frequency of the pulses of the electric current transmitted to each coil assembly is independently determined.

[0023] In some embodiments, each of the coils is shaped substantially as a triangular pyramid whose vertex has been truncated.

[0024] In some embodiments, each of the coil assemblies comprise two or more inter-nested coils such that an outer coil of one particular coil assembly at least partially shields the electromagnetic fields generated by an inner coil of the one particular coil assembly from coils of other adjacent coil assemblies.

[0025] In some embodiments, a total weight of the assembly is less than 100 kilograms.

[0026] In some embodiments, a total weight of the assembly is less than 30 kilograms.

[0027] In some embodiments, a total weight of one of the following modules is less than 10 Kgs: (i) a head module, (ii) an abdominal module, (iii) a thorax module and (iv) a legs module.

[0028] In some embodiments, a strength of the electromagnets is about 1.6 Tesla and the electromagnets are not permanent magnets.

[0029] In some embodiments, the coils comprise metallic tubes and further comprising a cooling system comprising water running through the tubes. In some embodiments, the portable assembly further comprises a series of projections that extend from an inner wall of the tubes so as to induce a water vortex in a flow of the water, wherein the water vortex increases an efficiency of the cooling system.

[0030] In some embodiments, the portable assembly further comprises a cooling fluid flowing through the coils and further comprising metal nanoparticles in the fluid configured to increase a signal to noise ratio for the transmitted signal.

[0031] In some embodiments, the power supply comprises a separate element of piezoelectric material for each of the electromagnets.

[0032] In some embodiments, the actuator is one or more of a pneumatic actuator, a hydraulic actuator and a chemical actuator. SH-MICH-008-PCT

[0033] In some embodiments, the power supply includes an adapter that has at least one of a rechargeable battery and a capacitor, so as to connect power to coils from external vehicles or stations.

[0034] In some embodiments, the electromagnets are not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

[0035] A further embodiment is a portable assembly for an MRI imaging system configured to accommodate human adults and children, comprising a scanner bore; electromagnets, including a core and an RF coil assembly, situated along an inner wall of the scanner bore; a power supply configured to generate pulses of electric current and an electromagnetic field; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject inside the scanner bore during a hiatus between the pulses and to transmit the signal to a remote computer system for one or more of an image and an analysis; at least one of: (a) an adjustment mechanism for a radial adjustment of the scanner bore comprising a series of pneumatic actuators situated along an inner wall of the scanner bore; and (b) a precision adjustment mechanism for the radial adjustment of the scanner bore comprising a series of electromechanical actuators situated along the inner wall of the scanner bore, wherein a radius of the scanner bore is configured to be adjusted by the one or more adjustment mechanisms.

[0036] In some embodiments, the electromechanical actuators are situated between coils of the electromagnets so as to precisely position each coil of the electromagnet taking into account a breathing, heartbeat and unconscious micromovements of the subject.

[0037] In some embodiments, the inner wall of the scanner bore comprises circumferentially or radially collapsible sections between the electromagnets pursuant to the adjustment mechanism.

[0038] In some embodiments, a first and a third of a series of the electromagnets faces in a first direction and a second of the series of electromagnets faces in a direction opposite to the first direction. In some embodiments, each of the electromagnets are shaped substantially as a truncated pyramid.

[0039] In some embodiments, the scanner bore is radially adjustable by one or more of (i) a pneumatic adjustment mechanism and (ii) an electromechanical adjustment mechanism.

[0040] In some embodiments, the scanner bore comprises multiple modules that are each independently radially adjustable. In some embodiments, the multiple modules include at least two SH-MICH-008-PCT of (i) a head module, (ii) a thorax module, (iii) an abdominal module, (iv) chest module and (v) a leg module. In some embodiments, each of the multiple modules is independently radially adjustable as a result of having one or both of the series of pneumatic actuators and the series of electromechanical actuators. In some embodiments, the portable assembly further comprises a head module that has from 32 to 36 of the electromagnetics.

[0041] In some embodiments, a quantity of the electromagnets is a number from 16 to 256 and wherein each of the electromagnets comprises a coil assembly. In some embodiments, each of the coil assemblies comprise two or more inter-nested coils such that an outer coil of one particular coil assembly at least partially shields the electromagnetic fields generated by an inner coil of the one particular coil assembly from coils of other adjacent coil assemblies.

[0042] In some embodiments, the power supply comprises a mixture of materials that includes piezoelectric crystals.

[0043] In some embodiments, the power supply is configured to generate 3 to 300 pulses per second.

[0044] In some embodiments, each of the electromagnets includes a metallic coil and further comprising a cooling system that includes water circulating inside the metallic tubes. In some embodiments, the water has metal nanoparticles suspended in the water for increasing a signal to noise ratio for the transmitted signal. In some embodiments, the water is hydrogenated water so as to increase a signal noise ratio of the transmitted signal. In some embodiments, the metallic tubes have a series of projections that extend from an inner wall of the tubes so as to induce a water vortex in a flow of the water, wherein the water vortex increases an efficiency of the cooling system.

[0045] In some embodiments, one or more of a frequency, a duration, a power and a polarization of the pulses of the electric current transmitted to each of the electromagnets is independently determined by virtue of being connected to a computer controller.

[0046] In some embodiments, the coils of each of the electromagnets are immersed in a heatabsorbing mixture so as to increase a heat capacity of the immersed electromagnet.

[0047] In some embodiments, a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

[0048] A still further embodiment is a portable assembly for an MRI imaging system, the assembly comprising a scanner bore having an inner wall; electromagnets positioned along the inner wall, SH-MICH-008-PCT each electromagnet comprising a metallic core surrounded by a coil assembly; each of the coils comprise metallic tubes, the assembly further comprising a cooling system that includes water running through the tubes for cooling the electromagnets; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject inside the scanner bore and to transmit the signal to a remote computer system for generating one or more of an image and an analysis, wherein at least one of the following is true:

[0049] (i) the water is hydrogenated water;

[0050] (ii) the water contains suspended nanoparticles; and

[0051] (iii) projections extend from an inner wall of the tubes to induce a water vortex.

[0052] In some embodiments, the projections extend from the inner wall of the metallic tubes at an acute angle to the inner wall in relation to a flow of the water and are shaped to induce the water vortex to increase an efficiency of the cooling system.

[0053] In some embodiments, the metallic tubes have a variable cross-section so as to induce the water vortex in a flow of the water, the water vortex configured to increase an efficiency of the cooling system.

[0054] In some embodiments, the water has the metal nanoparticles suspended in the water so as to reduce a signal to noise ratio of the transmitted signal.

[0055] In some embodiments, the portable assembly further comprises a built-in power supply connected to each of the electromagnets, the power supply comprising piezoelectric material and an actuator, the power supply controlled by a controller so as to generate pulses of electric current at a specified frequency and for a specified duration. In some embodiments, the power supply is configured to generate pulses of 6000 milliseconds or less. In some embodiments, the power supply is configured to generate 3 to 300 pulses per second. In some embodiments, the power supply is configured to produce a current of 10 to 300 amperes. In some embodiments, each of the pulses is between 3.3 milliseconds and 333 milliseconds in duration. In some embodiments, a frequency of the pulses of the electric current transmitted to each coil is independently determined. In some embodiments, a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image. SH-MICH-008-PCT

[0056] A yet still further embodiment is a portable assembly for an MRI imaging system, the assembly configured to accommodate human adults and children, the assembly comprising: a scanner bore divided into at least two modules from among (i) a head module, (ii) a thoracic module, (iii) an abdomen module and (iii) a leg module; for each module of the at least two modules, the modules include: electromagnets situated along an inner wall of the module; a power supply controlled by a controller so as to generate pulses of electric current at a specified frequency and for a specified duration; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject in the scanner bore during a hiatus between the pulses and to transmit the signal to a remote computer system for analysis, wherein each of the at least two modules is configured to independently and simultaneously perform an MRI scan and transmit data regarding a result of the MRI scan to the remote computer system for analysis.

[0057] In some embodiments, the scanner bore is divided into at least three modules from among (i) the head module, (ii) the thoracic module, (iii) the abdominal module and (iv) the legs module.

[0058] In some embodiments, the scanner bore is radially adjustable by one or more of (i) a pneumatic adjustment mechanism and (ii) an electromechanical adjustment mechanism.

[0059] In some embodiments, each of the at least two modules is radially adjustable.

[0060] In some embodiments, the portable assembly further comprises, for each of the at least two modules, at least one of the following adjustment mechanisms:

[0061] (a) an adjustment mechanism for a radial adjustment of the module comprising a series of pneumatic actuators situated along the inner wall; and

[0062] (b) a precision adjustment mechanism for the radial adjustment of the module comprising a series of electromechanical actuators situated along the inner wall of the module, wherein a radius of the module is configured to be radially adjusted by the one or more adjustment mechanisms.

[0063] In some embodiments, the power supply comprises piezoelectric crystals and is connected separately and independently to each of the electromagnets. SH-MICH-008-PCT

[0064] In some embodiments, the power supply is a piezoelectric battery configured by the controller to supply electrical impulses to the electromagnets so as to generate a specific amount of power in a controlled sequence.

[0065] In some embodiments, a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

[0066] Another embodiment is a portable assembly for an MRI imaging system, the assembly comprising: a scanner bore having an inner wall; electromagnets positioned along the inner wall, each electromagnet comprising a metallic core surrounded by a coil assembly, the coil assembly comprising one or more coils made of a metal and graphene; a power supply configured to generate pulses of electric current, at a specified frequency and for a specified duration, and an electromagnetic field; detectors positioned along the inner wall and configured to detect a reflected signal from a tissue of a subject inside the scanner bore, and to transmit the signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis, wherein the generated pulses are of a duration of a second or less.

[0067] In some embodiments, each coil of the coil assembly comprises a metal layer, a graphene layer and a ceramic layer.

[0068] In some embodiments, the coil assembly comprises at least two coils and comprises liquid nitrogen situated in a space between adjacent coils of the at least two coils.

[0069] In some embodiments, the liquid nitrogen is at a temperature of minus 185° C or higher.

[0070] In some embodiments, each electromagnet is superconductive.

[0071] In some embodiments, the power supply comprises pyroelectric piezoelectric material and an actuator, the power supply controlled by a controller so as to generate the pulses of electric current at the specified frequency and for the specified duration.

[0072] In some embodiments, the duration of the pulses is less than 100 milliseconds.

[0073] In some embodiments, the duration of the pulses is between 3 milliseconds and 333 milliseconds and wherein the number of pulses per second is 3-300.

[0074] In some embodiments, a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image. SH-MICH-008-PCT

[0075] A further embodiments is a method of calibrating frequencies for an MRI imaging system, the method comprising: using electromagnets of a coil assembly, connected to an inner wall of a scanner bore, to emit toward a subject a first set of signals at a first frequency that represents a reference frequency for MRI imaging of a particular body portion and processing the first set of signals to generate a first set of images; using the electromagnets to emit toward the subject a second set of signals at a frequency higher than the first frequency and a third set of signals at a frequency lower than the first frequency, and processing the second set of signals and the third set of signals to generate a second set of images and a third set of images; selecting a best set of images from among the second set first image and the third set of images by comparing a quality of the second set of images with a quality of the third set of images, or by comparing the first set of images with each of the second set and the third set of images; emitting a set of one or more signals at an adjusted frequency that was used to generate the best set of images; and determining a final frequency by adjusting the adjusted frequency as many times as necessary to approach a resonance frequency of the subject's tissue being scanned.

[0076] In some embodiments, the determining of the final frequency by adjusting the adjusted frequency as many times as necessary to approach the resonance frequency is implemented by comparing as many times as necessary a quality of a set of images generated from a signal emitted at a most current adjusted frequency with a quality of a set of images generated from a signal emitted at a new frequency selected to be higher or lower than the most current adjusted frequency.

[0077] In some embodiments, the method further comprises selecting the new frequency by taking into consideration previously rejected frequencies.

[0078] In some embodiments, the method further comprises using a power supply connected to each of the electromagnets to generate pulses of electric current and an electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration; and using sensors / detectors positioned along the inner wall and configured to detect a signal derived from changes in a tissue of a subject inside the scanner bore, the changes responsive to the electromagnetic field, and to transmit the signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis, wherein the generated pulses are of a duration of a second or less.

[0079] Another embodiment is a method of manufacturing ceramic superconductive electromagnets, the method comprising: inputting yttrium barium copper oxide powder and aluminum oxide powder SH-MICH-008-PCT into a 3-D printer; programming the 3-D printer using 3-D printing design software to output a ceramic coil in the form of a tube in which a layer of aluminum oxide surrounds a layer of yttrium barium copper oxide; heating the ceramic coil in an oven at a temperature of at least 300°C for at least 18 hours; and slow cooling the ceramic coil for at least 18 hours.

[0080] In some embodiments, the method further comprises inserting liquid nitrogen into a cavity of the tube of the ceramic coil such that the liquid nitrogen is hermetically sealed.

[0081] A still further embodiment is a method of MRI imaging, comprising: scanning a portion of a subject using electromagnets positioned along an inner wall of a scanner bore such that the electromagnets are positioned so as to be colinear and so that the electromagnets emit a signal to tissue of the subject, wherein a reflected signal from the tissue is detected by detectors and transmitted to a computer system to initially construct a three-dimensional image; and converting, by the computer system, the three-dimensional image into a two-dimensional image.

[0082] In some embodiments, the method further comprises outputting, by the computer system, one or more of (i) an analysis of the two-dimensional image and (ii) a diagnosis based on the two- dimensional image.

[0083] In some embodiments, a quantity of the electromagnets is a number from 16 to 256 and wherein each of the electromagnets comprises a coil assembly.

[0084] In some embodiments, the method further comprises using a power supply connected to each of the electromagnets to generate pulses of electric current and an electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration, wherein the generated pulses are of a duration of a second or less.

[0085] In some embodiments, the computer system is remote and the electromagnets are part of a portable assembly.

[0086] In some embodiments, the method further comprises using the two-dimensional image to determine a precise localization of a defect in the subject's body. In some embodiments, the defect is in a brain of the subject.

[0087] A yet still further embodiment is a method of MRI imaging, comprising: scanning a portion of a subject using electromagnets positioned along an inner wall of a scanner bore such that the electromagnets are positioned so as to not be coplanar and so that the electromagnets emit a signal to tissue of the subject, wherein a reflected signal from the tissue is detected by detectors and SH-MICH-008-PCT transmitted to a computer system to initially construct a three-dimensional image; and converting, by the computer system, the three-dimensional image into a two-dimensional image.

[0088] In some embodiments, the method further comprises using the two-dimensional image to determine a precise localization of a defect in the subject's body.

[0089] BRIEF DESCRIPTION OF THE DRAWINGS

[0090] Various embodiments are herein described, by way of example only, with reference to the accompanying drawings, wherein;

[0091] Fig. 1A is a schematic view of a head module of scanner bore of an assembly for a portable MRI imaging system showing a patient inside part of a scanner bore, in accordance with one embodiment;

[0092] Fig. IB is a schematic view of several module of the scanner bore of an assembly for a portable MRI imaging system showing a patient inside part of a scanner bore, in accordance with one embodiment;

[0093] Fig. 1C is a schematic of a portable assembly for an MRI imaging system containing multiple modules that are configured to function independently and / or simultaneously, in accordance with one embodiment;

[0094] Fig. ID is a schematic of a portable assembly showing an adjustable scanner bore for the head module, in accordance with one embodiment;

[0095] Fig. IE is a top view of the bottom layer of a cover with embedded detectors for use in a portable assembly for a head module, in accordance with one embodiment;

[0096] Fig. IF is a schematic view from the side and front of a subject covered by a cover with embedded detectors for use in a portable assembly for a head module, in accordance with one embodiment;

[0097] Fig. 1G is a schematic view from the side of a subject covered by a cover with embedded detectors for use in a portable assembly for multiple modules, in accordance with one embodiment;

[0098] Fig. 1H1 is a schematic view showing a configuration of electromagnetic coils that are arranged in a curved configuration, including multiple pairs, situated so as to generate an initial three- dimensional image, in accordance with one embodiment; SH-MICH-008-PCT

[0099] Fig. 1H2 is a schematic view showing a configuration of electromagnetic coils that includes multiple arrays situated so as to generate an initial three-dimensional image in conjunction with a movable support structure, in accordance with one embodiment;

[0100] Fig. 2A is a schematic horizontal sectional view of the thoracic module of the scanner bore and depicting a series of electromagnets in the form of truncated pyramids, in accordance with one embodiment;

[0101] Fig. 2B is a schematic top view of a series of electromagnets used in the thoracic module of the assembly of Fig. 2A, in accordance with one embodiment;

[0102] Fig. 3A is a schematic horizontal sectional view of the thoracic module of the scanner bore and depicting a series of electromagnets in an alternative configuration of the truncated pyramids, in accordance with one embodiment;

[0103] Fig. 3B is a schematic top view of the alternative configuration of the series of electromagnets used in the thoracic module of the assembly of Fig. 3 A, in accordance with one embodiment;

[0104] Fig. 4 is a schematic view of the coils of an electromagnet used in the assembly for a portable MRI imaging system, in accordance with one embodiment;

[0105] Fig. 5 is a schematic view of a truncated pyramidal shape of a core of an electromagnet around which the coils are wrapped to form the truncated pyramidal electromagnet used in an assembly for an MRI imaging system, in accordance with one embodiment;

[0106] Fig. 6 is a schematic illustration showing a cooling liquid supply system with galvanic isolation from the coils and a pyro-piezoelectric power supply, for a portable MRI imaging system, in accordance with one embodiment;

[0107] Fig. 7 is a workflow of an assembly for a portable MRI machine or system, in accordance with one embodiment;

[0108] Fig. 8A is a partial longitudinal cross-sectional view of a coil tube of an electromagnet that includes graphene, in accordance with one embodiment;

[0109] Fig. 8B is a longitudinal cross-sectional view of a coil of a superconductive ceramic electromagnet that includes yttrium barium copper oxide, in accordance with one embodiment;

[0110] Fig. 8C is a longitudinal cross-sectional view of a coil tube of an electromagnet that has a variable cross-section, in accordance with one embodiment;

[0111] Fig. 9 is a flow chart showing a method, in accordance with one embodiment; SH-MICH-008-PCT

[0112] Fig. 10 is a flow chart showing a method of producing a superconductive electromagnet coil, in accordance with one embodiment; and

[0113] Fig. 11 is a flow chart showing a method of MRI imaging, in accordance with one embodiment.

[0114] DETAILED DESCRIPTION OF THE EMBODIMENTS

[0115] The following detailed description is of the best currently contemplated modes of carrying out the invention. The description is not to be taken in a limiting sense, but is made merely for the purpose of illustrating the general principles of the invention, since the scope of the invention is best defined by the appended claims.

[0116] Applicant has discovered that it is possible to have a portable MRI imaging system that is lightweight and compact enough to be conveniently placed and used in (i) an ambulance and other land vehicles, aircraft and spacecraft (ii) a military vehicle on the battlefield such as an armored personnel carrier and (iii) in a person's home. In contrast, the prior art stationary and portable MRI systems cannot be used in these environments.

[0117] Applicant has also discovered that it is possible and useful to have MRI imaging systems that are tailored to the individual patient's size, in contrast to the prior art.

[0118] The superconducting magnet systems and the permanent magnet systems of static MRI imaging systems generate a lot of heat and are very heavy (and expensive). Furthermore, current portable MRIs weigh at least 635 Kgs. Current MRIs - whether stationary or portable - also do not have scanner bore that are adjustable in diameter (or length). Consequently, a small or very young person's scanned body or body part would be too far away from the emitters to generate images of the highest quality.

[0119] Applicant has further determined that the water distribution within a person's body varies from person to person and over the course of time. It also varies from one part of the body of a particular person to another part of that person's body. In addition, it varies over time within the same human body part. Applicant believes that it would be useful to have MRI imaging systems that are tailored to the patient's own distribution of water within their body. Since the hydrogen ion of the water molecule is used by MRI imaging systems as an indicia for the presence of body tissue, and since the water distribution varies over time and varies spatially within a person's body and from SH-MICH-008-PCT person to person, the frequency (or resonance frequency) emitted by the MRI system for scanning a subject's body or organ can be tailored to the actual water distribution of that organ or person.

[0120] According to certain embodiments, the portable MRI imaging system assembly of the embodiments herein weighs 100 Kgs or less, for example in some embodiments 80 Kgs or 80-100 Kgs or 100 Kgs. In certain embodiments, MRI imaging system assembly can be as low as seven Kgs by exploiting the use of graphene or an alloy of graphene and metal instead of metal.

[0121] In contrast to the prior art, the portable assembly for the MRI imaging system does not utilize a permanent magnet. It does not generate constant electricity but rather pulses of electricity for short periods of time such as 3.3 milliseconds up to 333 milliseconds or less than 100 milliseconds (or 20-40 milliseconds). In one non-limiting version, from 3 to 300 pulses per second are utilized. The use of brief pulses of electricity results in far less heat being generated. This in turn results in a much simpler cooling system, and in some embodiments a cooling system without any condensers. This reduces the weight (and volume) even further. It further reduces the length in each dimension and the maximum length in any dimension. The "maximum length in any dimension" means the magnitude of the length of the dimension that has the greatest length from among the height, width and length.

[0122] A "break" is an interval during which the electric current is off, i.e. there is no pulse of electric current. The interval is either bounded by two pulses (one before and one after the interval) or, if the pulse is at the beginning or at the end of the period being examined, the interval is bounded on one side by a pulse and on the other side by the beginning or the end of the measurement period, as the case may be.

[0123] It is also imperative to check the exact location of a defect in the brain before initiating neuronal stem cell cellular rehabilitation for stroke victims. Precision is critical for achieving the best rehabilitation outcomes.

[0124] MRI imaging systems do not currently produce 3-D images of the brain without first reconstructing 2-D slices. Rather, they take images in planes and the resulting 2D images are reconstructed into a 3-D model. Even alternative technologies such as Diffusion MRI (dMRI) and Functional MRI (fMRI) that provide additional information also require pre-processing and reconstruction of the data, which still requires producing intermediate 2-D slices. SH-MICH-008-PCT

[0125] In prior art MRI imaging systems, an initial image is in 2-dimensions and the image is then converted to 3-dimensions. This has numerous drawbacks. One is that the conversion software makes a well-known error called a partial voluming artifact. This is a common artifact in MRI imaging that occurs when a voxel within the image contains a mixture of different tissue types or structures. This affects the process of constructing a 3-D image from the 2-D image. This error has implications in being able to precisely localize the defect such as the location of a blood clot caused by a cerebral vascular accident (CVA) (stroke) as a prerequisite to implementing neuronal stem cell cellular rehabilitation. 2-D images may contain noise or artifacts that can worsen the reconstruction. It is impossible to completely eliminate these unwanted effects and they can negatively affect the final quality of the 3-D image.

[0126] Another drawback is the information loss from starting with 2-D images since the 2-D images may not contain all the necessary information about the spatial arrangement of brain structures. If the 2-D images do not cover the entire brain volume or have insufficient resolution, this may reduce the accuracy of 3-D reconstruction, which can lead to distortion or loss of important details. Deformation of structures may also occur during reconstruction, especially if there are significant changes in shape or contour when moving from 2-D to 3-D. A still further drawback is that the process of reconstructing a 3-D image based on 2-D slices requires complex processing algorithms and can be labor-intensive, increasing the risk of errors. A still further drawback is that structural variations between individuals may not be accounted for in the reconstruction process, which may result in models that do not reflect the anatomical features of a particular patient. Yet another drawback is that 3-D reconstruction results may require additional validation using other imaging modalities, which adds steps to the analysis process and increases the overall time and resource costs.

[0127] Applicant has discovered a way of reducing this artifact in MRI imaging and avoiding the other drawbacks. The helps creating more precise localization needed for the rehabilitation. This improved localization also has implications in other neurological conditions as well, including Alzheimer's and movement disorders.

[0128] The portable MRI scanning assembly, in some embodiments, does not include the computer system that creates the image and / or analyzes the image or diagnoses the patient. The portable MRI imaging assembly is instead connected to remote computer systems that provide the images and / or analysis of the data outputted by the assembly. SH-MICH-008-PCT

[0129] The portable assembly for the MRI imaging system, in some embodiments, is suitable for use by nonphysicians. Certain embodiments that achieve a very low weight such as less than 10 Kgs can be used virtually anywhere.

[0130] In certain embodiments, it is possible to maintain the quality of the MRI image comparable to a 3T stationary MRI machine while dramatically reducing the weight so as to make it accessible to battlefield vehicles, ambulances and even homes. Furthermore in some embodiments, the quality is simultaneously maintained while avoiding having to shield the room or vehicle containing the MRI assembly.

[0131] In certain embodiments, for example those in which the frequency emitted by the electromagnets is customized in accordance with the water concentration of the subject or the subject's body part or body portion, the quality may be even greater than that of a stationary MRI machine having a 3T magnet.

[0132] In some embodiments, the MRI assembly 10 and system is lightweight and achieves extreme mobility and provides more accessibility that prior art MRI imaging systems. For example, assembly 10 may have a weight as low as 7-16 kg. Assembly 10 may fit into a regular backpack. Assembly 10 maybe easily carried even by an untrained person, robot or dog and in some versions may cost orders of magnitude less than a stationary MRI imaging system, less than the Hyperfine® portable system with much better quality. The assembly 10 or system may also take about one minute to deploy and may have its own independent power supply, thereby being independent of, and avoiding the need for, stationary power sources (as a result of the set of piezoelectric power supply elements), a feature that is valuable in hard-to-reach and extreme conditions.

[0133] In some embodiments, portable assembly 10 is disposable.

[0134] "Resonance frequency" refers to a frequency of the signal emitted from the body tissue of the subject (during an MRI imaging process in response to the signal from the MRI imaging assembly) that is the frequency of the highest amplitude.

[0135] "About" means plus or minus 10%.

[0136] The principles and operation of a Lightweight Portable MRI Assembly according to the invention may be better understood with reference to the drawings and the accompanying description. SH-MICH-008-PCT

[0137] As seen from Fig. IB, in a portable assembly 10 for MRI imaging, a patient 15 is resting on a support structure 16 inside a scanner bore 20 of the assembly 10. The assembly 10 may form part of an MRI imaging system in that assembly 10 interacts with a remote computer system 98. As seen from Fig. 1 A, Fig. ID and from Fig. 2A, the scanner bore 20 has an inner wall 26. The inner wall 26 defines an internal surface whose horizontal cross-section (wherein the "horizontal" direction is perpendicular to a longitudinal direction running parallel to the length of the subject's body) may be circular, substantially circular, curved, partially curved, substantially curved, oval, substantially oval, rectangular, substantially rectangular, or any other shape that is fully or partly curved and partly not curved or not curved.

[0138] As seen from Fig. 1 A, Fig. IB and Fig. 1C, the entire scanner bore 20 can be viewed as separate modules associated with body portions of the subject being scanned including one or more of a head module 21 (Fig. 1A), a thoracic module 22 (Fig. IB, Fig. 1C), an abdomen module 23 (Fig. IB, Fig. 1C), a legs module 24 (Fig. IB, Fig. 1 C) or other body portion modules such as a chest module or a pelvic module. Each module of the scanner bore 20 may comprise one or more sections of the wall of the scanner bore, each section of the one or more sections of the wall being referred to as a belt 30. Especially in the case of a tall subject, there may be more than one belt 30 for a particular module.

[0139] Although Fig. IB and Fig. 1C depict scanner bore 20 modules as discrete and separated by a space, the length (along the length of the patient's body) of each module may be adjustable such that the scanner bore 20 depicted in these figures may lengthen so as to reduce or eliminate the gaps between the modules 21, 22, 23, etc. and thereby result in a continuous or essentially continuous wall (for example the inner wall 26) or a wall that at least appears to an outside observer to be continuous. Another option is that the wall of the scanner bore is continuous along the length of the bore 20 such that the modules 21, 22, 23, 24 are not structurally distinct but rather are defined by the distinct "volumes" of space that are scanned, (i.e. the space around the head, the space around the thorax, the space around the legs, etc.).

[0140] Inner wall 26 may be curved although not necessarily circular. Alternatively, the inner wall 26 is partly rectangular and party curved or substantially rectangular and curved, for example, at its corners. In this case, inner wall 26 may be partly curved or curved in portions of the belt 30. Alternatively, inner wall 26 is rectangular or substantially rectangular. SH-MICH-008-PCT

[0141] The term "circumferential" portion of the inner wall 26 is used herein to refer to the internal surface of the inner wall 26 regardless of whether the shape of such inner wall 26 is circular, substantially circular, curved, partially curved, substantially curved, oval, substantially oval, rectangular, substantially rectangular or any other shape that is fully or partly curved or not curved.

[0142] Fig. 2A is a schematic horizontal sectional view cut at some point along the length of the thoracic module 22 of the scanner bore 20. The viewer is looking axially as a result of the cut. Fig. 2A depicts a schematic axial view of the thickness of the belt 30. As seen in Fig. 2A, the assembly 10 may include electromagnets 40 that may be positioned circumferentially along the inner wall 26. In certain embodiments, each electromagnet 40 comprise a metallic core 42 surrounded by a coil assembly 44. Coil assembly 44 (and other coil assemblies) may be held in place by a coil holder frame 39 (Fig. 1H1).

[0143] Fig. 2A shows a series of electromagnets 40 shaped in the form of truncated pyramids, according to one embodiment, attached to the belt 30 within a thickness of the belt 30.

[0144] Fig. 3A is a top view looking from outside the scanner bore 20 through the belt 30 toward the space where the patient would be situated for a scan. Fig. 3A shows these electromagnetics 40 in a particular non-limiting configuration designed to maximize space efficiency.

[0145] In Fig. 3B, the electromagnets 40 are shown in an alternative non-limiting configuration. In both Fig. 2B and in Fig. 3B, a first and a third (or more) of a series of the electromagnets faces in a first direction and a second (or a second and a fourth or more) of the series of electromagnets faces in a direction opposite to the first direction. Inner wall 26 may comprises portion that are considered belts including a first belt

[0146] As shown in Fig. 2AA, each electromagnetic 40 may include a coil assembly 44 wrapped around a core 42, such as an iron core (even though the core 42 is depicted in only one of the electromagnets 40 shown in Fig. 2A). The core's own coil 43 is attached to and integrated with the core 42, as depicted in Fig. 1 A. The term "coil assembly" 44 as used in this patent application means one or more coils of a particular electromagnet 40 other than coil 43 of the core 42. In Fig. 2A each of the one or more coils which together comprise coil assembly 44 has been designated 44A (inner coil) and 44B (outer coil) (and there could be further coils more radially distant than outer coil 44B) SH-MICH-008-PCT

[0147] In some embodiments, the coil assembly 44 comprises two or more inter-nested coils 44A (inner coil), 44B (outer coil) such that an outer coil 44B of a particular coil assembly 44 at least partially shields the electromagnetic fields generated by the inner coil 44A of that coil assembly 44 (and may also at least partially shield coil 43 of core 42) from coils of other coil assemblies 45, 46, 47, 48, 49, 50, 51 (Fig. 2A) that are adjacent (for example adjacent along the inner wall of the scanner bore 20 or of a particular portion of the scanner bore 20 associated with a particular module (e.g. 21, 22, 23, 24, 25 etc.) to coil assembly 44, for example coils 45A, 45B of coil assembly 45 and coils 46A and 46B of coil assembly 46. Fig. 4 also shows two electrically conducting connectors 43 configured to connect to a power supply (not shown).

[0148] Coils 44 A (or 44 A and 44B or 44 A, 44B, 44C, etc.) of coil assembly 44 (and of other coil assemblies 46, 48 etc.) may be formed as coiled tubes. The composition of the material that coils 44A are made from may vary. In some embodiments, the coil tubes are made from metal such as copper. In certain embodiments, the tubes are made from a combination of metal and graphene, for example 50% each. In certain embodiments, the tubes are made from a combination of metal, graphene and a composite or alloy of metals such as copper, aluminum, silver, brass and magnesium, as shown by Fig. 8A and Fig. 8B. In some implementations of this, as shown by Fig. 8C, the tubes have a variable cross-section (diameter) and may be prepared by winding a variable cross-sectional graphene material for example by hand or otherwise and then sprayed (or otherwise layered) with nanometer sized metal that may be alloys for example alloys comprising one or more of copper, aluminum, silver, brass (which is an alloy of copper and zinc) and magnesium.

[0149] In some embodiments, the number of windings of the coil 44A, 44B, etc. will not exceed 318 and will be at least about 20 or 30 or 32.

[0150] Electromagnets 40 are configured to emit frequencies, for example radio frequencies, in the range 0.1 MHz (100 KHz) to 10 MHz. The actual frequency can be adjusted by adjusting various parameters associated with the piezoelectric elements of the power supply 50, which may also affect the length of time of the pulses, using controller 60 controlling the power supply 50.

[0151] Instead of continuous electricity, the electromagnets 40 generate pulses of electric current for short periods of time such as one three-hundredth of a second to one third of a second. .

[0152] In some embodiments, during any given second of time, the length of the pulse or pulses of electric current is less than 100 milliseconds. In some embodiments, during any given second of time, the length of the pulse or pulses of electric current is less than 50 milliseconds. The length of the SH-MICH-008-PCT pulses may be increased by placing capacitors between coils 44 and piezoelectric elements 52. In some embodiments, during any given second of time, there are 3 pulses pers per second or 333 pulses per second or in other embodiments 3000 pulses per second or 6000 pulses per second.

[0153] In some embodiments, the length of any pulse is less than half the length of the break (as defined herein) following that pulse (assuming there is a break after the pulse) and less than half the break immediately before that pulse (assuming there is a break before the pulse). In some embodiments, the length of any pulse is less than 0.1 of the length of the break following that pulse (assuming there is a break after the pulse). Without being bound by theory, the following technical details are provided as one particular non-limiting example of how to achieve the performance of the coils in some embodiments of an assembly 10 for a portable MRI:

[0154] The weight (approximate) of the coils (with the length of one face at the base 110-300 mm, at the cut top 100-270 mm and the height of 110-230 mm):

[0155] - Copper wire (diameter 3-5 mm): ~ 5-17.6 kg

[0156] - Copper tube (diameter 5-7 mm, wall thickness 1 mm): ~ 4-16.9 kg

[0157] -Graphene tube (5mm diameter, silver-plated, 82% graphene, 18% silver)): ~2-7.25kg

[0158] -YBCO (yttrium barium copper oxide) tube (diameter 7mm, wall thickness 1mm): ~3.5- 11.9kg

[0159] To achieve a magnetic field of 0.1 - 1 T using the available power of a piezoelectric battery of 25 - 250 kW, about 32-318 turns are needed for each coil, (while the number of coils, depending on the configuration of the system, can be from 2 to 96 or more). This value is the same for all materials, since it depends on the current and the length of the coil.

[0160] Effect of ferrite cores:

[0161] • Magnetic permeability (p ): Ferrite materials have a high magnetic permeability (p r), which can be hundreds or thousands of times greater than that of a vacuum (pO ).

[0162] • Magnetic field formula with ferrite: B= LpO -pr -NT Where is: o pr is the relative magnetic permeability of a ferrite core.

[0163] Effects on coil performance:

[0164] 1. Increase in magnetic field: In the presence of a ferrite core, the magnetic field (B) increases proportionally p r .

[0165] 2. Reduced number of turns: To achieve the same magnetic field (0.1 T), the number of turns can be significantly reduced. SH-MICH-008-PCT

[0166] 3. Reduced amperage: Similarly, it is possible to reduce the amperage if the number of turns remains the same.

[0167] In other words, by using different brands and configurations of ferrites, coil configurations and materials, configurations and materials of pyropiezoelectric cells, and monitoring and control systems, it is possible to sufficiently facilitate the configuration and optimization of portable MRI.

[0168] As seen from Fig. 5, in some embodiments, each entire electromagnet 40, which includes its core 42 and its coil assembly 44, is shaped like a pyramid whose vertex has been truncated. The core alone also may be shaped substantially like a truncated pyramid.

[0169] The core 42 of electromagnet(s) 40 produce an electromagnetic field that extends to the subject located in the scanner bore 20. This field affects the protons (or other targeted molecules / atoms such as deuterium or carbon or oxygen) in the tissue of the patient, and in particular in the water of the tissue. The affect includes changes, for example alignment, in the angle of spin of the protons, etc.

[0170] The sequence of electric pulses generated by the power supply 60 has an effect on the protons or other elements (deuterium, carbon, oxygen) being targeted while such protons or other elements are under the influence of the magnetic field. When a particular pulse of electric current ceases, the energy signal released by the tissue of the signals, for example the energy released by the protons of Hydrogen (or by another element (in the tissue of the subject) such as deuterium being targeted) is detected by detectors 70. The assembly 10 may include detectors 70 that may be positioned circumferentially along the inner wall 26. The detectors 70 may be configured to detect a signal of energy released by elements in the tissue of a subject 15 located inside the scanner bore 20 at a frequency of between 0.1 MHz (100 KHz) and 10 MHz inclusive.

[0171] In some embodiments, as shown in Fig. IE, many detectors 70 may be embedded into a cover 19 configured to be wrapped around the subject or wrapped around a body part of the subject 15 that is to be scanned in a particular module 21, 22, 23, 24, 25. In one non-limiting implementation shown in Fig. IE, which shows only the bottom layer 19b of cover 19 with the detectors above this layer (the top layer 19a shown in Fig. IF) MRI signal detectors 70 are embedded between each ply or layer of a two ply or two layer thickness cover 19. As shown in Fig. IF, cover 19 may be a sheet of linen or cloth or other suitable material that is configured to cover the supine subject 15 comfortably without interfering with the breathing of the subject 15. SH-MICH-008-PCT

[0172] In some embodiments, as shown in Fig. IF, detectors 70 in cover 19 are situated between the bottom layer 19a (for example made of rubber) of cover 19 and an air space layer under top layer 19a (for example made of linen or fabric or cloth) of cover 19 such that the act of pumping air using pump 17 into the air space by means of micro-compressor 18 (at a pressure of for example of about 0.5 atm pressure) urges the detectors 70 downward toward the body of subject 15, as seen from the pathway from micro-compressors 18 on the right side of Fig. IF leading to the cover 19. As also seen from Fig. IF, there is also a pathway from the micro-compressors 18 on the left side of Fig. IF leading to the top of the mattress where additional detectors 70 are located. This pumps air into an air space of the mattress to press detectors 70 upwardly toward the body of the subject 15.

[0173] As shown in Fig. 1G, in some embodiments, a micro-compressor 18a is configured to facilitate the pumping of air into the cover 19 to press detectors 70 downward toward the subject's body and a micro-compressor 18b is configured to facilitate the pumping of air into an air space (a) in the mattress 14 to generate upward pressure on detectors 70 located below the subject 15 and (b) in a head pillow 29, so that detectors move closer to the body of subject 15.

[0174] In some embodiments, unlike in Fig. IF, cover 19 is separate for each module 21, 22, 23, 24, 25. In some embodiments, a different cover 19 may be used for each subject 15. Alternatively, cover 19 may be sterilized for hygienic reasons by exposing the surfaces of layers 19a, 19b of cover 19 to UV radiation.

[0175] As shown in Fig. 1H1 (and Fig. 1A), the electromagnets 40 of assembly 10, in any embodiment, may be arranged such that the combination of three or more of these electromagnets 40 comprises multiple pairs or groups of electromagnets 40 (including coils) so as to generate three- dimensional images (initially). In one non-limiting implementation shown in Fig. 1H1, a pair of electromagnets 40 (called "fronto-parietal occipital" in Fig. 1H1) has an electromagnet positioned facing the frontal lobe and the second electromagnet of the pair positioned facing either the occipital lobe or the parietal lobe of the subject's brain. In a second pair of electromagnets 40, one electromagnet in the pair faces a left side of the temporal lobe and the other faces the right side of the temporal lobe. In a third pair of electromagnets 40, one electromagnet in the pair faces a left side of the frontal lobe and the other faces the right side of the frontal lobe. One, or an array 40 A, of electromagnets 40 faces the parietal lobe. Another pair of electromagnets 40 (called "oblique frontoparietal" in Fig. 1H1), comprises one electromagnet 40 that faces the left side of the frontal lobe and SH-MICH-008-PCT one electromagnet 40 that faces the right side of the parietal lobe. Due to the nonlinear, circular positioning of the electromagnets 40 in the implementation shown in Fig. 1H1, the patient 15 need not be moved by the assembly 10 in order to capture three-dimensional holographic images.

[0176] In a further non-limiting implementation shown in Fig. 1H2 the electromagnets 40 containing the electromagnets 40 including their coils are arranged in multiple, for example three arrays including an array 40A and a pair of arrays 40A-40A. Although each array of the three arrays, taken by itself, may comprise linearly arranged electromagnets 40, the electromagnets 40 in the third array 40 A shown in Fig. 1H2 are not colinear or even necessarily coplanar with those of the pair of arrays 40A-40A. Moreover, in this version, the support structure 16 on which the patient 15 is resting and therefore also the patient 15 are configured to be moved by an actuator, for example by an engine 16A, through up to three degrees of freedom relative to the electromagnets 40 in the three arrays 40 A. The three degrees of freedom are exemplified in Fig. 1H2 by the x-axis, the y-axis and the z-axis, along which or around which such motion occurs. Although Fig. 1H2 is depicted mainly to show stationary arrays 40A of electromagnets 40 and a movable support structure 16, the reverse is also possible (a stationary support structure 16 and movable arrays 40A, 40A-40A of electromagnets 40).

[0177] Detectors 70 may be any suitable MRI sensor for detecting aspects of the elements (e.g. Hydrogen protons, deuterium, carbon, oxygen or other elements) such as Tl— T2 relaxation time, phase shift, motion (such as intracranial pulsations) the angle of the flip of the protons or other elements of the subject's tissue (or other useful aspects) that are reflected back to detectors 70 as a signal from the subject's tissue when the radio frequency signal (or other frequency) emitted by the coils 44 (or coil assembly 44) is turned off (i.e. when the pulse ceases).

[0178] In one non-limiting example, detectors are radio frequency (RF) receivers. In another nonlimiting example detectors 70 are NV detectors such as artificial diamonds or other materials with NV centers. NV centers in diamonds are special defects in the crystal lattice, where a carbon atom is replaced by a nitrogen atom, and one atom is missing next to it (vacancy). These centers have quantum spin states, which are very sensitive to external magnetic fields. When a diamond with NV centers is illuminated with a laser, the spin state of the NV centers changes with the magnetic field, and these changes can be read using optical fluorescence.

[0179] Detectors 70 may be very small. For example, NV detectorss may be less than 1.0 mm, SH-MICH-008-PCT allowing them to be used in imaging applications where small size is important. Lasers may be used to excite NV centers, and fluorescence is then monitored using photodetectors. This approach allows the use of high-precision quantum effects to detect weak magnetic fields.

[0180] Detectors are configured to be sensitive to a frequency of 0.1 MHz (100 KHz) to 10 MHz.

[0181] Detectors 70 may be configured to transmit the detected signal directly to a remote computer system 98 (Fig. ID) that generates at least one of an image, an analysis and / or a diagnosis. In that case the remote computer system 98 may include analog to digital converters. Detectors 70 may instead be configured to transmit the detected signal indirectly to a remote computer system 98 (Fig. 1 A, Fig. IB). In this case, the detectors 70 are configured to transmit the signal to a data collection and transmission unit 88 that creates data packets that are then transmitted through to the remote computer system 98 in any sequence. Initially, the digitized signal in the form of data is stored on a memory storage unit of the data collection and transmission unit 88 as a data file. Data collection and transmission unit 88 may include a computer processor and software stored on memory for converting the data file into data packets for transmission in any sequence to the remote computer system. The transmission to the remote computer system for image generation and / or analysis may be implemented in a variety of manners including via communication networks (special communication networks, satellite Internet, tropospheric communication, a special cable) or even a flash drive carried by a messenger.

[0182] In one implementation, as shown in Fig. 6, a pyro-piezoelectric source 52 is under the control of controllers 60. A sequence of electrical pulses is generated from the piezoelectric source 52, which may be a pyro-piezoelectric source 52, and fed to coils of coil assemblies 44, 45, 46 of electromagnets 40 so as to generate a specific amount of power for each electromagnet in each module in a controlled sequence. A piezoelectric battery may feed power to electromagnetic coils with already specified characteristics and in a given sequence and does not require additional control.

[0183] In any embodiment of power supply 50, the mechanical irritation of the piezoelectric elements 52 (one non-limiting example of which are piezoelectric crystals 52) may occur at a frequency ranging from 3 times per second to 300 times per second. This is the internal resonance of the piezoelectric element. This frequency of 3-300 Hz is the frequency with which the mechanical actuator, such as a piston, is pushed by a pneumatic drive, a hydro drive or a pyrotechnic drive, and SH-MICH-008-PCT thereby mechanically affects the package ("sandwich") of mixtures (paste, gel, powder) of piezoelectric substances 52. In one implementation, this mechanical irritation generates pulses of electric current exiting the package ("sandwich") of mixtures (paste, gel, powder) of piezoelectric substances 52 (and directed to the one or more coil assemblies 444, 45, 46, etc.) at a particular resonance frequency anywhere from 100 KHz to 10 MHz. When the electric current exits the power supply 50 (for example the piezoelectric material 52) it is transmitted to and reaches the electromagnet 40 and its coil assemblies 44, 45, 46, etc., such that in some embodiments the frequency of the coil assembly 44 may be the particular frequency between 100 KHz and 10 MHz. In other embodiments, the frequency is adjusted higher or lower (but still within the range of 100 KHz and 10 MHz) by means of a frequency regulator or adaptor, situated between the power supply 50 (or the piezoelectric material 52) and each of the one or more coil assemblies 44, 45, 46, etc.

[0184] In some embodiments, the power generated by the electromagnetic coils of the coil assemblies 44, 45, 46, etc. ranges from 50 KWatts to 300 KWatts. In some versions, the 300 KWatts is achieved by incrementally raising the power of the pulses up to 300. In this manner the length of the breaks between pulses is of less concern (due to the superconductivity) in some embodiments In some embodiments, the frequency is increased incrementally so that the power is increased from 50 KWatts to 300 KWatts.

[0185] In some embodiments, the voltage of the electricity in the coil assemblies (44, 45, 46 etc.) ranges from 100 Volt to 10 Kilovolt (KV) with an average voltage of about 300V or 500V. The current ranges from 10 amps to 300 amps with an average current of about 3331 to about 5001. This leads to a range of power from 1 KWatt to 3000 KWatts, with an average power of about 100 KWatts to 250 KWatts.

[0186] Coils of coil assemblies 44, 45, 46 may be made of a copper tube (and optionally also of aluminum, magnesium, silver, or a special alloy), the tube having a special variable cross-section. Inside the tube is a special cooling liquid - for example water or hydrogenated water in some cases including a suspension of nanoparticles fed from a nanoparticle storing source or a nanoparticle generating system. The cooling liquid 82 circulates under a certain pressure and at a certain speed.

[0187] Using coils of various configurations under the control of controller 60 and as a result of feeding a special sequence of pulses in a scanned volume within the scanning bore 20, there is created a multitude of small individual scanned volumes (along a given trajectory) whose sizes vary from 1 mm3 to 1 cm3. SH-MICH-008-PCT

[0188] As seen in Fig. 7, the received data are collected in data acquisition units or data collection units 88 (Fig. 7 blocks 8, 9, 10) which are configured to transmit this data (for example in some versions after creating data packets) through communication networks or systems 11 to block 13, which is the remote computer system in Fig. 7. The data acquisition and collection units 88 may include a receiver (Fig. 7 block 8) to receive the signal from detectors 70 (i.e. a radio frequency signal) and an analog digital converter (Fig. 7 block 9) and memory storage as well as software and hardware (Fig. 7 block 10) for collecting, creating and sending data files.

[0189] The coils 44, 45, 46 etc. may be sprayed with metal such as silver (or gold) in order to improve the ability of the coils to be cooled. The sprayed layer of metal may be external and / or internal

[0190] The coils 44, 45, 46 may be mounted in an inflatable frame, which minimizes the time of preparation of the system for operation and ensure its mobility.

[0191] Regarding the strength of the electromagnets 40 in assembly 10, there are several ways of implementing this. In one implementation, the strength of the electromagnets 40 (and therefore also the strength of the signal produced by the electromagnets 40 and reflected (from the subject's tissue) and received by the detectors 70) is boosted immediately to 1.6 T (Tesla) (for example by adjusting the electric current). The strength of the electromagnets 40 is high and the image quality is good. There is a relatively high signal to noise ratio with the resulting imaging having high contrast and spatial resolution. This can be further enhanced by adding nanoparticles into the water of the cooling system or by using hydrogenated water.

[0192] In another implementation regarding the strength of the electromagnets 40 in assembly 10, one starts with a Tesla strength of 50 milli Tesla and gradually increases the strength of the electromagnets 40 (and hence the strength of the signal) to a strength of 1.6 T, for example by increasing the current.

[0193] Increasing the strength of the electromagnet can be accomplished in one or both of the following two ways. One way is simply to increase the current. A second way is to use to increase the piezoelectric effect, for example by having the actuator contact (for example rub or deform) the piezoelectric material with greater force or frequency. In one version, the actuator exerts pressure on plates that sandwich piezoelectric crystals. SH-MICH-008-PCT

[0194] Either way the result is the same - a relatively high signal to noise ratio with the resulting imaging having high contrast and spatial resolution. This can be further emhanced by adding nanoparticles into the water 82 of the cooling system 80 or by using hydrogenated water.

[0195] Portable assembly 10 may also include a built-in power supply 50. Power supply 50 may be connected to each of the electromagnets 40. In one implementation, power supply 50 comprises piezoelectric materials such as pyroelectric piezoelectric material 52, for example solid materials, powders or creams. The piezoelectric material may be pyroelectric piezoelectric material. The material 52 may comprise crystals and / or ceramic or other solids including but limited to powders or viscous creams. The power supply 50 may also include actuators 54 that generate heat stress for example as a result of a mechanical action (such as pressing or rubbing or deforming) so as to affect or deform the pyroelectric material 52. In the case of piezoelectric material 52 that is not pyroelectric material, the actuator(s) 54 may be a mechanical actuator such as a movable plate or a pneumatic or a hydraulic actuator and may include plates that sandwich the piezoelectric material 52.

[0196] The power supply 50 may be configured to generate pulses of electric current and an electromagnetic field. In some embodiments, the power supply 50 comprises a separate element of piezoelectric material for each of the electromagnets 40.

[0197] One or more of a frequency, a duration, a power and a polarization of the pulses of the electric current transmitted to each of the electromagnets 40 is independently determined (in some embodiments using artificial intelligence) by virtue of being connected to the power supply 50 being connected to and / or controlled by computer controller 60.

[0198] In some embodiments, each of the electromagnets 40 in combination with the responsive detectors 70 may be considered as an independent scanning system.

[0199] Power supply 50 may be configured, based on controller 60, to determine a frequency of the pulses of the electric current transmitted to each coil assembly 44. In some implementations, the frequency of the pulses of the electric current transmitted to each coil assembly 44 is independently determined such as that different coil assemblies, and therefore different electromagnets 40, may have different pulse frequencies. This could be efficient where different modules 21, 22, 23, 24 of the scanner bore 20 are geared for different body parts and therefore require different frequencies (for example if the resonance frequencies of the body parts are different due to having different water concentrations). SH-MICH-008-PCT

[0200] Power supply 50 may be controlled by a controller 60 so as to generate the pulses of electric current at a specified frequency and for a specified duration. Controller 60 may control an actuator. The actuator may be one or more of a pneumatic actuator, a hydraulic actuator and a chemical actuator. The actuator may be a mechanical actuator that exerts pressure on the piezoelectric crystals or piezoelectric material. The actuator may for example exert pressure on plates that sandwich the crystals or piezoelectric material.

[0201] Such an actuator may be controlled by a processor and therefore the frequency and duration of the pulses of the electromagnetic coils 44 may be controlled. There are several non-limiting examples of how to accomplish this. For example, regulating the frequency of the magnetic field coils and other necessary parameters (amplitude, power and pulse duration, etc.) may be accomplished by controlling the power, speed, frequency, duration (quantity) and combination of all together of the pneumatic drive for mechanical action on the piezoelectric element or elements 52. Alternatively, combining the composition and quantity of piezoelectric mixtures. Alternatively, controlling the power, speed, frequency, duration (quantity) and combination of all together of a hydraulic drive for mechanical action on the piezoelectric element(s). Alternatively, controlling the power, duration, time and sequence of mechanical action on the piezoelectric element (elements) using pyrotechnic cartridges (supply of charges from a hom, box, tape, drum) due to partial removal of powder gases from the working cylinder (where the piston moves, acting on the piezoelectric element) or using a mechanism for feeding pyrotechnic cartridges similar to a "toothbrush" type mechanism for faster action. Or using a mixture of liquid or gaseous fuel and atmospheric air to set in motion and control the piston acting on the piezoelectric mixture.

[0202] The frequency of the electricity exiting the piezoelectric elements 52 and the frequency of the electromagnetic coils in the one or more coil assemblies 44, 45, 46, etc. will either be identical of, if a frequency regulator is inserted between the piezoelectric mixture 52 and the coils 44 in which case the frequency of the coils in the one or more coil assemblies 44, 45, 46, etc. will be higher or lower (but still within the range of the 100 KHz and 10 MHz).

[0203] One non-limiting implementation of a system or method for controlling pneumatic, hydraulic, pyroelectric and / or thermal drives is mechanical control systems with control programs in a form similar to a drum-cam system (for rough settings) and their combinations with electronic control systems for fine tuning of electric current characteristics. SH-MICH-008-PCT

[0204] In one non-limiting implementation of this, a drum or disk with cams mounted on the surface, which may be driven by a spring mechanism, similar to a clock, can rotate to activate various elements of the system in a given sequence, i.e. each cam closes or opens electrical contacts or pneumatic-hydraulic valves, or turns on or off the mechanism for feeding pyropatrons, or turns on or off the valves and contacts that control the operation of the heat engine (where the same piston moves, mechanically acting on the piezoelectric elements). Such a design is configured to reproduce complex programs specified physically with sufficient accuracy, and changing control programs is simple: it is enough to replace the disk, drum or tape with cams with another one and with a different program. By changing the size of the cams (height), their shape, the distance between them, the number of simultaneously read tracks with cams, such a drum, disk or tape can be adjusted to control the frequency, duration and amplitude of the pulses supplied to the drives (pneumatic, hydraulic, pyro- and thermal drives).

[0205] In a further non-limiting implementation, cycle cams may be configured to create a sequence of operations whereby different actuators and contacts are activated or deactivated at precisely defined intervals. This allows complex cycles of action on piezo elements 52 to be set up. This will also allow a single specific program to be repeated many times, which is suitable for setting pulse parameters such as frequency and duration at specified intervals.

[0206] In a further non-limiting implementation, Stepping drums with switches that are activated at each step. Such a drum can sequentially close and open electrical circuits, setting a program for each actuator. This allows for flexible control with more complex programs, since each step can correspond to a unique configuration, which is suitable for situations where a precise sequence is required, such as changing polarization or phase.

[0207] In a further non-limiting implementation, notched thumbwheel switches may be used in which a disc (mechanical, hydraulic or pneumatic) with notches on its surface rotates and each notch opens or closes a circuit which activates an actuator (pneumatic, hydro, pyro and thermal actuators). Controlling the rotation speed of the disc allows changing the duration and frequency of the pulses, which is suitable for systems where periodic repetition of pulses with the ability to be adjusted is required. This can be used to adjust the duration of the phases and the frequency of pulses in the case of sequential action on piezoelectric elements. In another non-limiting implementation, mechanical timers with movable cams move (adjustable) cams are configured to activate actuators SH-MICH-008-PCT in a given sequence and at different intervals. This allows setting complex time programs with the ability to be adjusted, which is well-suited for adjusting both the duration and frequency of pulses.

[0208] Power supply 50 may generate the electricity and the EMF field for short periods of time such as 3.3 milliseconds (one three hundredth of a second) up to 333 milliseconds (one-third of a second) or anything in between such as 32 milliseconds plus or minus 25%, or 3-50 milliseconds or 3-100 milliseconds or 20-40 milliseconds or 250 milliseconds or less or 333 milliseconds or less or 100-250 milliseconds or less than one second or 10-50 milliseconds.

[0209] In some embodiments, the number of pulses per second of electricity is 3 to 300. In embodiments in which the generated images are needed in the form of video, the number of piezoelectric elements used is increased (for example up to 20 such piezoelectric elements) (such as piezoelectric crystals) and as a result the number of pulses per second may be up to 3000, or in some embodiments, the number of pulses per second is 6000.

[0210] In some embodiments, the number of pulses generated per second is 30 or fewer In some embodiments, the number of pulses generated per second is three (or 3 or fewer). In some embodiments, the number of pulses per second is four (or 4 or fewer). In some embodiments, the number of pulses per second is two.

[0211] The power supply 50 may be configured to produce a current of 10 to 399 amperes. The power supply 50 may be configured to produce a voltage of 100V to 10 kilovolts. The power supply 50 may be configured to generate 1 to 3000 kilowatts.

[0212] Power supply 50 may include an adaptor 51 that has a rechargeable battery (an accumulator) and / or capacitors so as to connect the power to coils from external vehicles and external stations. The adaptor 51 may be used to connect to various types of equipment, for example, electrical equipment in a car, an armored personnel carrier, an aircraft, a recue drone, a land vehicle such as an ambulance or an armored personnel carrier, a spacecraft, a space station or other known electrical networks.

[0213] As shown in Fig. 4 and in Fig. 6, assembly 10 may also include a cooling system 80. In one implementation of the coils 44, the coils are tubular and comprise metal tubes (or graphene and metal) within which a cooling fluid runs. The cooling system 80 utilizes water 82 or another liquid (for example liquid nitrogen) running through these tubes. SH-MICH-008-PCT

[0214] In certain embodiments, as seen in Fig. 6, the efficiency of the cooling system 80 is enhanced by including a series of projections 84 that extend from an inner wall 26 of the tubes so as to induce a water vortex in a flow of the water 82. The water vortex increases an efficiency of the cooling system 80.

[0215] Nanoparticles 86, such as metal nanoparticles 86, have in some embodiments been added to the cooling fluid 82 (for example in the water 82) to increase a signal to noise ratio for the transmitted signal.

[0216] In one embodiment, the coils of coil assembly 44 are made in part (or completely) from graphene. Instead of fully metallic coils or tubes, one option is to use a combination of metal and graphene or a combination of metal and graphene and a particular ceramic to dramatically reduce the weight. This reduces the weight in two respects - one in that the graphene portion weighs less than metal (graphene is one sixth the weight of copper for example) and further that the use of graphene which has a high tensile strength allows for use of a thinner diameter "metallic" tubular coils. In some embodiments, this achieves a drastic weight reduction of the entire assembly to the point of weighing only seven (7) Kgs. It is noted that graphene acts like metal in that it can have greater electrical conductivity than copper and in that it has superior charge carrier mobility. Graphene is considered a quasi-metal. Furthermore, manufacturing technology currently exists (for example creating composites by mixing graphene with raw metal powder and then compacting into the desired shape) to integrate these two components so as to form an alloy of metal and graphene (for example 20% metal and 80% graphene).

[0217] For portable MRI assemblies described herein in any version, the percentage of metal in the mixture of metal and graphene used for the electromagnetic coils or coil assemblies 44 ranges from as low as 2% metal (and 98% graphene) to as high as 30% metal (and 70% graphene).

[0218] In one implementation of the coils for the electromagnets 40 of the portable assembly 10, as shown in the partial longitudinal cross-sectional view of Fig. 8A (showing for example a top half of the thickness of the tube / coil) each coil 44A, 44B, etc. in coil assembly 44 comprises several layers - Li, L2, L3, L4. For example, an outermost layer, Li, is made of metal (for example in the form of a powder), the adjacent layer, L2, is made of graphene (for example in the form of a powder), the next layer, L3, is made of a particular ceramic (for example in the form of a powder) and the innermost layer is made of metal (for example in the form of a powder). SH-MICH-008-PCT

[0219] In one non-limiting version, electromagnet 40 including core 42 and the layers of the coils of coil assembly 44 are manufactured using 3-D printing. 3-D printing is used to manufacture these layers of the coils of the coil assembly 44 and form the tubular coil. The powder layers are then heated in an oven at for example about 900 degrees Celsius and left to cool. The result is a coil tube. In Fig. 8A, the cavity of the coil 44A is denoted by reference numeral L . As noted, this cavity Ls may contain a fluid, for example liquid nitrogen.

[0220] In certain embodiments, coils 44A, 44B, etc. of coil assembly 44 of electromagnets 40 are made of a particular ceramic called yttrium barium copper oxide, whose preparation is known. This ceramic achieves superconductivity at lower temperatures than typical superconducting magnets that use liquid helium. Furthermore, this ceramic is far lighter than copper and even lighter than graphene.

[0221] As shown in the longitudinal sectional view of Fig. 8B, moreover, in some embodiments the yttrium barium copper oxide ceramic layer LA is insulated by an outer layer LB. The outer layer may be aluminum oxide (AI2O3) (for example corundum) or silicon carbide or silicon nitride or Teflon® or any of these with alternating layers of silicon dioxide. In certain embodiments, this insulated ceramic material is produced using 3-D printing. In some embodiments, the 3-D printing also places liquid nitrogen (or liquid nitrogen together with a smaller quantity of hydrogen) in the coil tubes. The preparation process may include steps in which after the insulation layer LB is added to the yttrium barium copper oxide material layer LA the combined material is heated in an oven, for example at approximately 300°C for approximately 24 hours, and then removed and allowed to slow cool, for example for approximately 24 hours. The result is a material that is not brittle, unlike prior art superconducting ceramics, which are very brittle. Furthermore, the material is very lightweight.

[0222] The coils 44A, 44B, 44C, etc. are part of a coil assembly 44 that may contain as many as 8 inter-nested coils. Each nested coil 44A, 44B, 44C, 44D, etc. is made of the above multiple layers. Typically the coolant (water or liquid nitrogen) is within the tubular coils of the one or more coil assemblies but optionally, if the coolant is liquid nitrogen, this liquid nitrogen may fill the space between the inter-nested coils 44A, 44B, 44C etc. The liquid nitrogen is cooled to a temperature than is hotter than minus 200° C, in some embodiments, hotter than minus 185° C. The liquid nitrogen is cooled to a temperature of about minus 183° C in some embodiments. The liquid nitrogen is configured to cool the metal (for example copper), the ceramic and the graphene to be approximately the same temperature as the liquid nitrogen. Applicant has discovered that the SH-MICH-008-PCT introduction of the liquid nitrogen at approximately minus 183° C (plus or minus 7 degrees C) will form a superconductive effect. Without being bound by theory, this should cause the electrical resistance of the ceramic to go down towards zero - and hence the electrical resistance of the metal and graphene will likewise decline to or towards zero. Importantly, this superconductive effect may be achieved by using a fluid cooled to only about 183° C as opposed to a fluid cooled all the way down to 270° Celsius such as by using liquid helium. This lowers the cost of manufacturing considerably, in only due to the very expensive nature of liquid helium.

[0223] In some versions of method 200, there is a step of inserting liquid nitrogen in a cavity of the tubular coil, wherein the liquid nitrogen is hermetically sealed.

[0224] The remote portion of the system not shown in the drawing includes the computer system that receives the transmitted signal from the data collection unit 88 or from detectors 70 and creates an image and analyzes the image. This computer system may use specialized software for MRI. For example, Nordic Neuro Lab offers specialized software for MRI data analysis, including functional MRI (fMRI) and image processing. This specialized software is often used in research and clinical settings and is available at https: / / www.nordicneurolab.com. In addition, the following specialized software, https: / / www.osirix-viewer.com / called OsiriX is a program for processing and analyzing MRI and CT images. It is widely used by radiologists and researchers to view and process medical images - it can be used to process and generate the images from the signal transmitted to the remote computer system in the embodiments described herein for the portable MRI imaging assembly. In addition, https: / / mri.medicine.uiowa.edu / equipment-information / research-facility-software called

[0225] MRI Research Facility Software — University of Iowa MRI Image Analysis Software Toolkit can be used for analysis of the images. This software includes FSL, AFNI, Slicer3 and other instruments designed for research purposes.

[0226] In some embodiments, scanner bore 20 is radially or circumferentially adjustable. As shown in Fig. 2A and Fig. 3 A, along the inner wall 26, there may be spaces along the band between the electromagnets or between the detectors. A series of actuators, for example pneumatic actuators, may be situated between the electromagnets 40, or between the coil assemblies 44 of the electromagnetics 40, in order to effectuate an adjustment of a diameter or circumference of the scanner bore 20. In some embodiments, electromechanical actuators are situated between coils of the electromagnets so as to precisely position each coil of the coil assembly 44 of the electromagnet SH-MICH-008-PCT

[0227] 40. In some versions, the positioning is configured to take into account a breathing, heartbeat and / or unconscious micromovements of the subject. In one implementation shown in Fig. ID, assembly 10 includes a central electromechanical actuator (such as a gear 94) from which multiple connecting levers 95 extend to portions of the wall 20A of the scanner bore 20 for precise adjustment of the diameter or circumference of the scanner bore 20. Wall 20A includes the different portions thereof (for example wall portion 21 A of head module 21) in the event that the various modules 21, 22, 23, 24, 25, etc. are spaced apart from one another.

[0228] Assembly 10 may include an adjustment mechanism for the scanner bore 20 or for particular modules 21, 22, 23, 24 etc. of the scanner bore 20. In one implementation, assembly 10 has at least one of:

[0229] (a) an adjustment mechanism for a radial adjustment of the scanner bore comprising a series of pneumatic actuators situated along an inner wall of the scanner bore (for example situated between electromagnetics 40); and

[0230] (b) a precision adjustment mechanism for precise tuning or subsequent fine tuning of the radial or circumferential adjustment of the scanner bore 20 comprising a series of electromechanical actuators situated along the inner wall 26 of the scanner bore 20, wherein a diameter of the scanner bore is configured to be adjusted by the one or more adjustment mechanisms.

[0231] The electromechanical actuators are situated between the electromagnets coils 44A, 44B, etc. so as to precisely position each coil 44A, 44B, etc. of the coil assembly 44, taking into account the patient's breathing, heartbeat and unconscious micromovements.

[0232] Inner wall 26 of the scanner bore 20 may have circumferentially or radially collapsible sections between the electromagnets pursuant to the adjustment mechanism.

[0233] The scanner bore 20 may comprise multiple modules 21, 22, 23, 24 that are each independently radially adjustable. The multiple modules may include at least two or at least three of or all four of (i) a head module 21, (ii) a thorax module 22, (iii) an abdominal module 23, (iv) chest module and (v) a leg module 24. Each of the multiple modules may be independently radially adjustable as a result of having one or both of the series of pneumatic actuators and the series of electromechanical actuators. SH-MICH-008-PCT

[0234] In some embodiments, the head module 21 has from 32 to 36 of the electromagnetics. The quantity of the electromagnets in the assembly 10 is a number from 16 to 256 and each of the electromagnets comprises a coil assembly.

[0235] As seen from Fig. 2B and Fig. 3B, in one particular non-limiting embodiment, a first and a third of a series of the electromagnets faces in a first direction and a second of the series of electromagnets faces in a direction opposite to the first direction.

[0236] One or more of a frequency, a duration, a power and a polarization of the pulses of the electric current transmitted to each of the electromagnets is independently determined by virtue of being connected to the computer controller 60.

[0237] One embodiment of assembly 10 is a portable assembly for an MRI imaging system that includes: a scanner bore having an inner wall; electromagnets positioned along the inner wall, each electromagnet comprising a metallic core surrounded by a coil assembly; each of the coils comprise metallic tubes, the assembly further comprising a cooling system that includes water running through the tubes for cooling the electromagnets; detectors positioned along the inner wall and configured to detect a signal of an electromagnetic field and to transmit the signal to a remote computer system for generating one or more of an image and an analysis, wherein at least one of the following is true:

[0238] (iv) the water is hydrogenated water;

[0239] (v) the water contains suspended nanoparticles; and

[0240] (vi) projections extend from an inner wall of the tubes to induce a water vortex.

[0241] The projections may extend from the inner wall of the metallic tubes at an acute angle to the inner wall in relation to a flow of the water and are shaped to induce the water vortex to increase an efficiency of the cooling system.

[0242] As shown by Fig. 8C, the metallic tubes of coils or coil assemblies 44 may have a variable cross-section so as to induce the water vortex in a flow of the water, the water vortex configured to increase an efficiency of the cooling system. SH-MICH-008-PCT

[0243] In any embodiment herein, the coils or coil assemblies 44 of each of the electromagnets 40 may optionally be immersed in a heat-absorbing mixture (e.g., a salt mixture) so as to increase a heat capacity of the immersed electromagnet, for example by twenty or more times that of water.

[0244] As shown in Fig. 1C, another embodiment of the assembly 10 is a portable assembly for an MRI imaging system, the assembly 10 configured to accommodate human adults and children. The assembly 10 shown in Fig. 1C depicts a scanner bore 20 divided into multiple (two or more) modules from among (i) a head module 21, (ii) a thoracic module 22, (iii) an abdomen module 23 and (iv) a leg module 24. Each of the multiple modules may include electromagnets 40 situated along an inner wall 26 of the module. Assembly 10 may also include a power supply 50 controlled by a controller so as to generate pulses of electric current at a specified frequency and for a specified duration and detectors 70 positioned along the inner wall and configured to detect a signal of an electromagnetic field from the electric current and to transmit the signal to a remote computer system for analysis. Power supply 50 may be inside base 93. In that case, there would be apertures (not shown) that allow thin cable to connect from power supply 50 to the electromagnets 40 and their coil assemblies 44.

[0245] Each of the modules is configured to independently perform an MRI scan. The scanning by the head module 21 of the subject's head may be performed without regard to whether another module of assembly 10 may be scanning the subject's legs, thorax or abdomen, for example, and so on for all of the modules in assembly 10. Moreover, each of the modules is also configured to simultaneously perform an MRI scan while one or more other modules of assembly 10 performs an MRI scan. Each of the modules of assembly 10 is also configured - once the scan occurs - to transmit data regarding the results of the MRI scan to the remote computer system 98 for analysis.

[0246] Furthermore, the adjustment feature of the bore modules 21, 22, 23, 24 (and module 25 or other modules in certain embodiments), wherein the module is for example radially adjustable or circumferentially adjustable, is shown in Fig. ID with respect to head module 21. It is also noted that in some embodiments the adjustment of a portion of the bore 20 (and hence the diameter or volume of the space inside the module) of the modules of assembly 10 is independent of the adjustment of one or more of the other modules of assembly 10.

[0247] Fig. ID shows one particular adjustment mechanism 90 for electromechanical adjustment of any of the modules of the assembly 10. In this mechanism 90, the portion of the scanner bore 20 that is part of head module 21 can be implemented as an expandable helmet 21 A. In some SH-MICH-008-PCT embodiments, as shown in Fig. IB, there may be one or more soft pillow elements made of soft material 29, or filled with air between the subject's head and the inner wall 26 of the helmet 21 A (which is the inner wall 26 of the head module 21. Air compressor 29A (Fig. IB may be used to control the volume of air in these pillows 29. This is to fixate the subject's head.

[0248] As shown in Fig. ID, the helmet 21 A is surrounded by a helmet holder 21B that may sit on a base, which may be a general control box that may incorporate the power supply 50. Fig. ID depicts an adjustment mechanism 90 for radially or circumferentially adjusting the size of a head module 21. This adjustment mechanism 90 is equally applicable to other modules 22, 23, 24, 25, etc. that may form part of assembly 10. Adjustment mechanism 90 is specifically configured to adjust the diameter or volume inside the scanner bore of a module of assembly 10, for example of head module 21.

[0249] As shown in Fig. ID, adjustment mechanism 90 may be electromechanical. The electromechanical adjustment mechanism 90 shown in Fig. ID may include one or more micro engines 91, which may be situated in any location from which they can effectuate their purpose as described below. The micro engines 91, or an on / off switch 92 that controls the micro engines 91 may be in an outer portion of the helmet 21 A. An on / off switch 92 for the micro engines may be positioned in a base 93 of the head module 21, although this is one example of where such a switch can be.

[0250] As shown in Fig. ID, micro engines 91 are configured to move, for example to turn, one or more gears 94 that are integrated with levers 95 whose distal end may face in a direction toward the subject being scanned, or in particular the subject's head 17. The distal end of each of levers 95 may penetrate and attach to the wall 20 A of the bore 20 of head module 21. Wall 20 A includes inner wall 26 and outer wall 27. The turning of gears 94 in one particular direction pulls levers 95 and exerts a force pulling wall 20A outward. As a result of the accordion-like shape of accordion portions 28 of wall 20 A, this outward force drives wall 20A to actually move outward whereby such accordion-like portions 28 change shape to a simple curve like the rest of wall 20A (as shown in Fig. ID). Guides 99 serve to guide the outward movement of walls 21 A and include a lock to hold such walls 21 A in place in the expanded position.

[0251] Conversely, a movement of gears 94 in a reverse direction - which can be initiated by micro engines 91 as controlled by their ON / OFF switch - reverses the expansion of walls 21 A and collapses walls 20A such that the walls 20A move inwardly. It is readily apparent that an outward SH-MICH-008-PCT movement of walls 20A increases a diameter and volume of the space within the walls 20A and that an inward movement decreases such diameter and volume. This is one non-limiting way in which adjustment mechanism 90 can operate.

[0252] In some implementations, the scanner bore is divided into at least two or at least three or all four modules from among (i) the head module 21, (ii) the thoracic module 22, (iii) the abdominal module 23 and (iv) the legs module 24.

[0253] One further embodiment of assembly 10 is a portable assembly for an MRI imaging system, the assembly comprising: a scanner bore 20 having an inner wall; electromagnets 40 positioned along the inner wall, each electromagnet comprising a metallic core surrounded by a coil assembly 44, the coil assembly 44 comprising one or more coils 44A, 44B etc. made of a metal and graphene; a power supply 50 configured to generate pulses of electric current, at a specified frequency and for a specified duration, and an electromagnetic field; detectors 70 positioned along the inner wall and configured to detect a signal derived from changes in a tissue of a subject inside the scanner bore, the changes responsive to the electromagnetic field, and to transmit the signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis; wherein the generated pulses are of a duration of a second or less.

[0254] Any of the other features may be incorporated into this embodiment. As one example, any version of cooling system 80 may be incorporated into this embodiment (or into any other embodiment that does not explicitly mention the cooling system 80). As another example, any version of the adjustment mechanism 90 may be incorporated into this embodiment.

[0255] As shown in Fig. 8 A, each coil of the coil assembly 44 may comprise a metal layer, a graphene layer and a ceramic layer.

[0256] In some versions, each electromagnet 40 is superconductive. For example, the coil assembly 44 comprises at least two coils and liquid nitrogen is situated in a space between adjacent coils of the at least two coils 44A, 44B, etc. of coil assembly 44. This liquid nitrogen may be hermetically sealed in place. The liquid nitrogen may be at a temperature of minus 185° C or higher, for example minus 183°C. This provides an advantage over the prior art superconductive elements (for example those that utilize helium) where a temperature of minus 270°C has to be reached in order to achieve SH-MICH-008-PCT superconductivity of the electromagnet. As a result of the superconductive effect, the resistance of the ceramic declines to zero. Since that happens to the ceramic it happens to the other materials of the tube of the coil of the electromagnet 40. An additional advantage of using liquid nitrogen to generate superconductive electromagnets for MRI imaging systems is that liquid nitrogen is cheap (in general) and abundant and in particular is far cheaper than helium.

[0257] At the time of the brief pulses (for example 32 milliseconds) the electromagnet 40 is akin to a permanent magnet, but this is achieved without the weight of a permanent magnet.

[0258] In some embodiments, power supply 50 comprises piezoelectric crystals or other materials or pyro-piezoelectric materials or crystals, and an actuator. The power supply may be controlled by a controller so as to generate the pulses of electric current at the specified frequency and for the specified duration.

[0259] The duration of the pulses may be 50 milliseconds or less, 100 milliseconds or less, 250 milliseconds or less or 500 milliseconds or less, or may be from 20 milliseconds to 50 milliseconds, for example 32 milliseconds plus or minus 10%.

[0260] The number of pulses per second is 3 or is less than 3, or in other embodiments is less than 2.

[0261] As shown in Fig. 9, another embodiment is a method 100 of calibrating frequencies for an MRI imaging system.

[0262] Method 100 may have a step 110 of using electromagnets 40 of a coil assembly 44 (or more than one coil assembly), for example a coil assembly 44 connected to an inner wall 26 of a scanner bore 20, to emit toward a subject a set of first signals, for example a first signal at a first frequency (for example a first radio wave frequency), at least two times, for example three times, the first frequency of the coils of the one or more coil assemblies 44, 45, 46, etc. selected based on previous MRI imaging experience or based on being accepted as a standard frequency for MRI imaging of the tissue of a particular body portion (or a subportion of that particular body portion) and processing the first (for example radio wave frequency) signal to generate at least two first images.

[0263] Let us suppose that we select 1.8 MHz as a starting reasonable frequency for one or more electromagnetic coils 44A, 44B (or 45 A, 45B or 46A, 46B) of the coil assemblies 44, 45, 46, etc., for example based on our experience or because it is often used for a particular portion of the body being scanned, or for some other reason such as being one of the frequencies that is or is close to an average or median resonance frequency for such tissue. Let us further suppose that the tissue inside the subject's head has a resonance frequency of 1.5 MHz. SH-MICH-008-PCT

[0264] The resonance frequency is that frequency with the highest amplitude of the signal that reflects back from the subject's tissue and is detected by a sensor or detector. The closer one approaches the actual resonance frequency, the better the quality of the image produced. This is because as the amplitude of the signal increases, the signal is stringer and of better quality (everything else being equal).

[0265] Continuing with that example, in order to find the resonance frequency of the subject's tissue being scanned, for example inside the cranium (as one non-limiting example), a set of three images are taken at a frequency of the one or more coil assemblies 44, 45, 46, etc. that is considered a standard frequency for head MRI imaging - in this case 1.8 Mhz. "A standard frequency" is any frequency published as a standard frequency for MRI imaging of that particular body portion (or subportion) that is accepted by the medical profession in the locale where the MRI imaging is occurring, or based on any other reasonable criteria. In some embodiments, instead of s standard frequency that has been accepted, any reference frequency is used based on the supposition of the technician and / or a supervising physician. In this case, the "standard frequency" may be replaced by the "reference frequency" in the discussion below and in method 100 in general. In some embodiments, the standard frequency or the reference frequency is selected by an artificial intelligence software program in the remote computer or in a computer system attached to the assembly 10.

[0266] Then a set of three more images are taken at a coil assembly frequency of 2.0 MHz, a higher frequency than the standard frequency used and in addition a set of three more images are taken at 1.6 MHz, a lower frequency than the standard frequency used. One then compares the quality of the images taken at 1.6 MHz to those taken at 1.8 MHz, and compares the quality of the images taken at 2.0 MHz to those taken at 1.8 MHz. If the images taken at 2.0 MHz are worse than those taken at 1.8 MHz and the images taken at 1.6 MHz are better than those taken at 1.8 MHz, a simple pattern is detected, for example by the remote computer system. One would therefore conclude that it is wise to continue the experiment by sampling three more images taken at a frequency lower than 1.6 MHz, namely for example 1.5 Hz. This process is continued by trial and error with or without the assistance of machine learning.

[0267] Alternatively, since the range of frequencies of the coil assemblies is assumed to be from 0.1 MHz to 10 MHZ, one option is to simply image the subject at 0.1 MHz and then at a higher frequency such as 0.2 MHZ and then at a higher frequency of 0.3 MHZ until we find that the image SH-MICH-008-PCT quality that is the best (or we try 2 MHz, then 3 MHz, then 4 MHz, then 5 MHz, then 6 MHz, then 7 MHz, then 8 MHz, then 9 MHz, then 10 MHz until we find the ideal image quality).

[0268] Raising the frequency of the one or more coil assemblies 44, 45, 46, etc. may improve image quality but if one raises the frequency too much (and lowers the wavelength too much) then the depth of penetration of the signal declines. For example, at a frequency of 1.0 MHz or 3.0 MHz, one may obtain clear images of deep areas of the brain as well as of the brain cortex and other superficial portions of the brain; whereas at a frequency of 5 MHz or 6 MHz one may obtain very clear images of the brain cortex and other superficial areas of the brain but less clear images of the deep areas of the brain.

[0269] To find the optimal frequency, use trial and error by either artificial intelligence or a human technician or physician.

[0270] The optimal frequency for one person is not the optimal frequency for another person because each person has a different distribution of water in their tissue.

[0271] Accordingly, method 100 may also comprise another step 120 of using the electromagnets 40 to emit toward the subject a second set of signals (for example radio wave frequency signals) at a frequency higher than the first frequency and a third set of signals at a frequency lower than the first frequency, and processing the second set of signals and the third set of signals to generate a second set of images and a third set of images.

[0272] A further step 130 of method 100 may be selecting a best set of images from among the second set first image and the third set of images by comparing a quality of the second set of images with a quality of the third set of images, or by comparing the first set of images with each of the second set and the third set of images. For example step 130 may be implemented by selecting a best set of images from among the second set of images and the third set of images by comparing a quality of the first, second and third sets of images, for example by comparing a quality of the first set of images to a quality of the second set of images and by comparing a quality of the third set of images to a quality of the first set of images. Alternatively, the second and third sets of images may be compared.

[0273] Method 100 may also have a step 140 of emitting a set of one or more signals at the adjusted frequency that was used to generate the best set of images (in step 130).

[0274] Step 150 of method 100 comprises determining a final frequency by adjusting the adjusted frequency as many times as necessary to approach a resonance frequency of the subject's tissue SH-MICH-008-PCT being scanned. This may be implemented by determining a final frequency by adjusting the adjusted frequency as many times as necessary by comparing as many times as necessary a quality of a set of images generated from a signal emitted at a most current adjusted frequency with a quality of a set of images generated from a signal emitted at a new frequency selected to be higher or lower than the most current adjusted frequency.

[0275] Step 150 may alternatively be implemented for example by comparing as many times as necessary a quality of an images generated from a signal emitted at a most current adjusted frequency with a quality of an image generated from a signal emitted at a new frequency higher than and at a new frequency lower than the current adjusted frequency to arrive at a best newly adjusted frequency. In some embodiments, the best new frequency can be designed to be consistent with a direction of the change in frequencies during the last (most recently adjusted) adjustment of the frequencies.

[0276] For example, step 150 may involve repeating the above steps 110, 120, 130, 140 as part of a trial and error process to arrive at a final specified frequency. For example, a fourth set of images and a third set of images are obtained and compared to the most recent "best" frequency". The frequency of the image of better quality is then the new "best" frequency". This continues until a final frequency is reached. One way of finalizing the frequency is determining when the image quality reaches a preset threshold, for example a threshold of image resolution or other quantitative measure of quality. Another way is for the technician or physician to conclude that the image quality is subjectively satisfactory. Still another way is that the adjustments in the frequency are becoming smaller and smaller (for example based on a preset percentage of the change in frequency).

[0277] In some embodiments, machine learning and artificial intelligence are used in one or more of steps 110, 120, 130 and 150. If machine learning is used, then, in some cases, a supervised training dataset is created by machine learning. In one non-limiting example, a binary classification is made by an algorithm in comparing the quality of images generating by new frequencies with the quality of images generated by the most current adjusted frequency.

[0278] Method 100 may also involve using a power supply connected to each of the electromagnets to generate pulses of electric current and an electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration. The generated pulses may be of a duration of a second or less. SH-MICH-008-PCT

[0279] Method 100 may have a step of using sensors / detectors positioned along the inner wall 26 that are configured to detect a signal derived from changes in a tissue of a subject inside the scanner bore, the changes responsive to the electromagnetic field, and to transmit the signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis.

[0280] As a result of the design of the portable assembly 10, including but not limited to the fact that a permanent magnet is not used, and therefore the cooling system is much simpler, and the fact that the computer system used for analysis and image generation is remote, assembly 10 may have a weight of 100 Kgs or less. In some embodiments, the weight is 40 Kgs or less. In some embodiments in which graphene is used to replace metal coils, as described, the estimated weight of the entire assembly 10 is about 30 Kgs and the estimated weight of each module is 7.5 Kgs (plus or minus 10%).

[0281] In some embodiments, each coil has its own computer with an artificial intelligence system and transmits a signal to a common data system for the subsequent creation of a common data file and its transmission to common networks for imaging, examination, and diagnosis. The remote computer to which the data file is sent may also have software algorithms stored on a memory storage and configured to be executed by the remote computer system. These algorithms and / or software may include machine learning.

[0282] Outside the assembly 10, but part of the MRI scanning system, may be a hardware and software module 98 configured to interact with the detectors 70 (either directly as in Fig. ID or indirectly through data acquisition and transmission unit 88 as in Fig. 1 A and Fig. IB) so as to provide remote control of a scanning by the scanning bore 20, including remote configuration of scanning parameters and programs.

[0283] In some embodiments, there is also a hardware and software module for the preparation of specially prepared water (electrochemically cleaned water to obtain pure water and optionally with nanoparticles of chromium, nickel, iron and / or neodymium) for cooling the coils and, subsequently, specially contrasting liquids (i.e. liquid nitrogen), including those with a reduced (or zero content) gadolinium content, based on this specially prepared water with dispensers and individual dosage calculation, as well as specially prepared water and liquids to facilitate, improve, and activate the patient's excretory systems after the use of specially contrasting liquids.

[0284] In some embodiments the MRI system (or assembly 10) includes a hardware and software module with detectors for creating portraits of the subject, such as temperature, humidity and / or SH-MICH-008-PCT electrical portraits of the nervous system activity of the subject, sound portraits, portraits of micromotor activity, chemical portraits, pulse and respiration of the subject so as to be integrated with data from the MRI scan data files.

[0285] In one option, the electromagnets have an air cooling system including a Ranque-Hilsch vortex tube with an adapter that allows operation both from a compressed air cylinder and from various compressors. Other options have no compressor to diminish weight.

[0286] As shown in Fig. 10, a further embodiment is a method 200 of producing a ceramic superconductive coil for an electromagnet 40 for a portable assembly 10 of an MRI imaging system or machine. Method 200 may comprise a first step 210 of inputting yttrium barium copper oxide powder and aluminum oxide powder into a 3-D printer.

[0287] Step 220 may comprise programming the 3-D printer using 3-D printing design software to output a ceramic coil in the form of a tube in which a layer of aluminum oxide surrounds a layer of yttrium barium copper oxide.

[0288] Step 230 may comprise heating the ceramic coil in an oven at a temperature of at least 300°C for at least 18 hours.

[0289] Step 240 may involve slow cooling the ceramic coil for at least 18 hours.

[0290] As shown in Fig. 1H1 (and Fig. 1 A), the electromagnets 40 of assembly 10, in any embodiment, may be arranged such that the combination of three or more of these electromagnets 40 comprises multiple pairs or groups of electromagnets 40 (including coils) so as to generate three- dimensional images (initially). This was described with respect to assembly 10. In one non-limiting implementation shown in Fig. 1H1, a pair 40-40 of electromagnets 40 (called "fronto-parietal occipital" in Fig. 1H1) includes an electromagnet 40 positioned facing the frontal lobe and the second electromagnet of the pair positioned facing either the occipital lobe or the parietal lobe of the subject's brain. In a second pair 40-40 of electromagnets 40, one electromagnet 40 of a pair faces a left side of the temporal lobe and the other faces the right side of the temporal lobe. In a third pair 40-40 of electromagnets 40, one electromagnet 40 in the pair faces a left side of the frontal lobe and the other faces the right side of the frontal lobe. An array 40A of one or a group of electromagnets faces the parietal lobe. In a fourth pair 40-40 of electromagnets 40 (called "oblique fronto-parietal" in Fig. 1H1, one faces the left side of the frontal lobe and one electromagnet faces the right side of the parietal lobe. Due to the nonlinear positioning (for example circular positioning) of the SH-MICH-008-PCT electromagnets 40, the patient 15 or subject need not be moved by the assembly 10 in order to capture three-dimensional holographic images.

[0291] In the non-limiting implementation shown in Fig. 1H2, the electromagnets 40 containing the coils are arranged in multiple, for example three, substantially linear arrays 40A. The support structure 16 on which the patient 15 is resting is configured to be moved by an actuator through up to three degrees of freedom relative to the electromagnets 40, as shown by the three axes (x, y, z) in Fig. 1H2. As can be seen, two of the three arrays 40A form a pair 40A-40A.

[0292] As a result of either the implementation shown in Fig. 1H1 or that shown in Fig. 1H2, the electromagnets 40 with their coils are able to emit a signal that generates a three dimensional image rather than a two dimensional image. Accordingly, in some embodiments, the image generated by the remote computer system is initially a 3 -dimensional image, in contrast to the prior art, which does not directly generate a three-dimensional holographic image directly (but rather starts with a two-dimensional image that it has to first convert to a three-dimensional image). In that case, the remote computer system 98 then converts the holographic image into a two dimensional image. In this conversion process from 3-D to 2-D, the partial voluming artifact common to MRI imaging is significantly reduced and localization of a defect in the subject's body is more precise. Precise localization of a defect is particularly critical for brain injury. This localization is improved using the MRI imaging system or assembly 10 of the embodiments described herein in embodiments in which the initially obtained image is a three-dimensional image sent to remote computer system 98.

[0293] This contrasts with what current MRI imaging systems do, which is to begin with a 2-D image that is converted to 3-D. These systems do this because they use just two emitters to form the initial image or else they use more than two emitters and these three or more emitters are positioned in a linear configuration.

[0294] Accordingly, as shown in Fig. 11, one embodiment is a method 300 of imaging using an MRI imaging system, which may be used in any of the heretofore described embodiments. Method step 310 comprises scanning a portion of a subject using nonlinear or noncoplanar electromagnets 40 positioned (for example along an inner wall 26 of a scanner bore 20) such that a combination of the electromagnets 40 comprises multiple pairs or groups of electromagnets 40 positioned, for example as shown in Fig. 1H1 or Fig. 1H2, so as to generate three-dimensional images. The combination of such electromagnets 40 arranged in this way is configured to emit a signal to tissue of the subject, wherein a reflected signal from the tissue of the subject is detected (for example by detectors 70) SH-MICH-008-PCT and is transmited to a computer system 98 (which may be remote) to initially construct a three- dimensional image.

[0295] Step 320 comprises converting, by the computer system, the three-dimensional image into a two-dimensional image.

[0296] A further step may comprise outputting, by the computer system, one or more of (i) an analysis of the two-dimensional image and (ii) a diagnosis based on the two-dimensional image.

[0297] In some versions, the quantity of the electromagnets 40 may range from 16 to 256.

[0298] In some versions, each of the electromagnets 40 may comprise a coil assembly 10.

[0299] Some versions of method 300 may involve using a power supply 50 connected to each of the electromagnets 40 to generate pulses of electric current and an electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration, wherein the generated pulses are of a duration of a second or less.

[0300] In some versions, the computer system may be a remote computer system 98 and the electromagnets 40 may be part of a portable assembly 10 in accordance with any of the embodiments described herein.

[0301] Any of the details of the embodiments described herein may be combined with method 300.

[0302] In some versions, method 300 may be used also with a stationary MRI imaging system.

[0303] One embodiment is a method 400 of imaging using an MRI imaging system, which may be used in any of the heretofore described embodiments. Method step 410 comprises scanning a portion of a subject using electromagnets 40 positioned along an inner wall 26 of a scanner bore 20 such that a combination of the electromagnets 40 is not colinear, and the combination emits a signal to tissue of the subject, wherein a reflected signal from the tissue of the subject is detected (for example by detectors 70) and is transmitted to a computer system 98 (which may be remote) to initially construct a three-dimensional image.

[0304] Step 420 comprises converting, by the computer system, the three-dimensional image into a two-dimensional image.

[0305] A further step may comprise outputting, by the computer system, one or more of (i) an analysis of the two-dimensional image and (ii) a diagnosis based on the two-dimensional image.

[0306] Method 400 is identical to method 300 in all other respects (i.e. in all respects other than the configuration of the electromagnets being not colinear instead of being not coplanar). SH-MICH-008-PCT

[0307] While the invention has been described with respect to a limited number of embodiments, it will be appreciated that many variations, modifications and other applications of the invention may be made. Therefore, the claimed invention as recited in the claims that follow is not limited to the embodiments described herein.

Claims

SH-MICH-008-PCTWHAT IS CLAIMED IS:

1. A portable assembly for an MRI imaging system, the assembly comprising: a scanner bore having an inner wall; electromagnets positioned along the inner wall, each electromagnet comprising a metallic core that generates an electromagnetic field, the core surrounded by a coil assembly configured to emit a radio frequency (RF) signal to the subject; a power supply connected to each of the electromagnets, the power supply comprising piezoelectric material and an actuator, the power supply configured to generate pulses of electric current and the electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject inside the scanner bore during a hiatus between the pulses, and to transmit the reflected signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis, wherein the generated pulses are of a duration of a second or less.

2. The portable assembly of claim 1, wherein the power supply is configured to generate 3 to 300 pulses per second.

3. The portable assembly of claim 1, wherein the power supply is configured to generate 30 to 6000 pulses per second.

4. The portable assembly of claim 1, wherein the power supply is configured to generate 300 or fewer pulses per second.

5. The portable assembly of claim 1, wherein the power supply is configured to produce a current of 10 to 300 amperes.

6. The portable assembly of claim 1, wherein the power supply is configured to produce a voltage of 0.1 to 10 kilovolts.

7. The portable assembly of claim 1, wherein the power supply is configured to generate 1-3000 kilowatts.

8. The portable assembly of claim 1, wherein a frequency of the coil assembly is from 100 KHz to 10 MHz .

9. The portable assembly of claim 1, wherein the duration of each of the generated pulses is one third of a second or less.SH-MICH-008-PCT10. The portable assembly of claim 1, wherein the duration of each of the generated pulses is 3.3 milliseconds to 333 milliseconds.

11. The portable assembly of claim 1, wherein the scanner bore is radially or circumferentially adjustable.

12. The portable assembly of claim 1, further comprising each of a series of pneumatic actuators situated between the coil assemblies of the electromagnetics for adjustment of a diameter of the scanner bore.

13. The portable assembly of claim 12, further comprising a central electromechanical actuator from which multiple connecting levers extend to each of the coil assemblies for precise adjustment of a diameter or circumference of the scanner bore.

14. The portable assembly of claim 1, wherein a frequency of the pulses of the electric current transmitted to each coil assembly is independently determined.

15. The portable assembly of claim 1, wherein each of the coils is shaped substantially as a triangular pyramid whose vertex has been truncated.

16. The portable assembly of claim 1 , wherein each of the coil assemblies comprise two or more inter-nested coils such that an outer coil of one particular coil assembly at least partially shields the electromagnetic fields generated by an inner coil of the one particular coil assembly from coils of other adjacent coil assemblies.

17. The portable assembly of claim 1 , wherein a total weight of the assembly is less than 100 kilograms.

18. The portable assembly of claim 1, wherein a total weight of the assembly is less than 30 kilograms.

19. The portable assembly of claim 1 , wherein a total weight of one of the following modules is less than 10 Kgs: (i) a head module, (ii) an abdominal module, (iii) a thorax module and (iv) a legs module.

20. The portable assembly of claim 1, wherein a strength of the electromagnets is about 1.6 Tesla and the electromagnets are not permanent magnets.

21. The portable assembly of claim 1, wherein the coils comprise metallic tubes and further comprising a cooling system comprising water running through the tubes.SH-MICH-008-PCT22. The portable assembly of claim 21, further comprising a series of projections that extend from an inner wall of the tubes so as to induce a water vortex in a flow of the water, wherein the water vortex increases an efficiency of the cooling system.

23. The portable assembly of claim 1, further comprising a cooling fluid flowing through the coils and further comprising metal nanoparticles in the fluid configured to increase a signal to noise ratio for the transmitted signal.

24. The portable assembly of claim 1 , wherein the power supply comprises a separate element of piezoelectric material for each of the electromagnets.

25. The portable assembly of claim 1, wherein the actuator is one or more of a pneumatic actuator, a hydraulic actuator and a chemical actuator.

26. The portable assembly of claim 1 , wherein the power supply includes an adapter that has at least one of a rechargeable battery and a capacitor, so as to connect power to coils from external vehicles or stations.

27. The portable assembly of claim 1 , wherein the electromagnets are not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

28. A portable assembly for an MRI imaging system configured to accommodate human adults and children, comprising: a scanner bore; electromagnets, including a core and an RF coil assembly, situated along an inner wall of the scanner bore; a power supply configured to generate pulses of electric current and an electromagnetic field; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject inside the scanner bore during a hiatus between the pulses and to transmit the signal to a remote computer system for one or more of an image and an analysis; at least one of:(a) an adjustment mechanism for a radial adjustment of the scanner bore comprising a series of pneumatic actuators situated along an inner wall of the scanner bore; and(b) a precision adjustment mechanism for the radial adjustment of the scanner bore comprising a series of electromechanical actuators situated along the inner wall of the scanner bore,SH-MICH-008-PCT wherein a radius of the scanner bore is configured to be adjusted by the one or more adjustment mechanisms.

29. The portable assembly of claim 28, wherein the electromechanical actuators are situated between coils of the electromagnets so as to precisely position each coil of the electromagnet taking into account a breathing, heartbeat and unconscious micromovements of the subject.

30. The portable assembly of claim 28, wherein the inner wall of the scanner bore comprises circumferentially or radially collapsible sections between the electromagnets pursuant to the adjustment mechanism.

31. The portable assembly of claim 28, wherein a first and a third of a series of the electromagnets faces in a first direction and a second of the series of electromagnets faces in a direction opposite to the first direction.

32. The portable assembly of claim 31, wherein each of the electromagnets are shaped substantially as a truncated pyramid.

33. The portable assembly of claim 28, wherein the scanner bore is radially adjustable by one or more of (i) a pneumatic adjustment mechanism and (ii) an electromechanical adjustment mechanism.

34. The portable assembly of claim 28, wherein the scanner bore comprises multiple modules that are each independently radially adjustable.

35. The portable assembly of claim 34, wherein the multiple modules include at least two of (i) a head module, (ii) a thorax module, (iii) an abdominal module, (iv) chest module and (v) a leg module.

36. The portable assembly of claim 34, wherein each of the multiple modules is independently radially adjustable as a result of having one or both of the series of pneumatic actuators and the series of electromechanical actuators.

37. The portable assembly of claim 34, further comprising a head module that has from 32 to 36 of the electromagnetics.

38. The portable assembly of claim 28, wherein a quantity of the electromagnets is a number from 16 to 256 and wherein each of the electromagnets comprises a coil assembly.

39. The portable assembly of claim 38, wherein each of the coil assemblies comprise two or more inter-nested coils such that an outer coil of one particular coil assembly at least partially shields theSH-MICH-008-PCT electromagnetic fields generated by an inner coil of the one particular coil assembly from coils of other adjacent coil assemblies.

40. The portable assembly of claim 28, wherein the power supply comprises a mixture of materials that includes piezoelectric crystals.

41. The portable assembly of claim 28, wherein the power supply is configured to generate 3 to 300 pulses per second.

42. The portable assembly of claim 28, wherein each of the electromagnets includes a metallic coil and further comprising a cooling system that includes water circulating inside the metallic tubes.

43. The portable assembly of claim 42, wherein the water has metal nanoparticles suspended in the water for increasing a signal to noise ratio for the transmitted signal.

44. The portable assembly of claim 42, wherein the water is hydrogenated water so as to increase a signal noise ratio of the transmitted signal.

45. The portable assembly of claim 42, wherein the metallic tubes have a series of projections that extend from an inner wall of the tubes so as to induce a water vortex in a flow of the water, wherein the water vortex increases an efficiency of the cooling system.

46. The portable assembly of claim 28, wherein one or more of a frequency, a duration, a power and a polarization of the pulses of the electric current transmitted to each of the electromagnets is independently determined by virtue of being connected to a computer controller.

47. The portable assembly of claim 28, wherein the coils of each of the electromagnets are immersed in a heat-absorbing mixture so as to increase a heat capacity of the immersed electromagnet.

48. The portable assembly of claim 28, wherein a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

49. A portable assembly for an MRI imaging system, the assembly comprising: a scanner bore having an inner wall; electromagnets positioned along the inner wall, each electromagnet comprising a metallic core surrounded by a coil assembly; each of the coils comprise metallic tubes, the assembly further comprising a cooling system that includes water running through the tubes for cooling the electromagnets;SH-MICH-008-PCT detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject inside the scanner bore and to transmit the signal to a remote computer system for generating one or more of an image and an analysis, wherein at least one of the following is true:(vii) the water is hydrogenated water;(viii) the water contains suspended nanoparticles; and(ix) projections extend from an inner wall of the tubes to induce a water vortex.

50. The portable assembly of claim 49, wherein the projections extend from the inner wall of the metallic tubes at an acute angle to the inner wall in relation to a flow of the water and are shaped to induce the water vortex to increase an efficiency of the cooling system.

51. The portable assembly of claim 49, wherein the metallic tubes have a variable cross-section so as to induce the water vortex in a flow of the water, the water vortex configured to increase an efficiency of the cooling system.

52. The portable assembly of claim 49, wherein the water has the metal nanoparticles suspended in the water so as to reduce a signal to noise ratio of the transmitted signal.

53. The portable assembly of claim 49, further comprising a built-in power supply connected to each of the electromagnets, the power supply comprising piezoelectric material and an actuator, the power supply controlled by a controller so as to generate pulses of electric current at a specified frequency and for a specified duration.

54. The portable assembly of claim 53, wherein the power supply is configured to generate pulses of 6000 milliseconds or less.

55. The portable assembly of claim 53, wherein the power supply is configured to generate 3 to 300 pulses per second.

56. The portable assembly of claim 53, wherein the power supply is configured to produce a current of 10 to 300 amperes.

57. The portable assembly of claim 53, wherein each of the pulses is between 3.3 milliseconds and 333 milliseconds in duration.

58. The portable assembly of claim 49, wherein a frequency of the pulses of the electric current transmitted to each coil is independently determined.SH-MICH-008-PCT59. The portable assembly of claim 49, wherein a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

60. A portable assembly for an MRI imaging system, the assembly configured to accommodate human adults and children, the assembly comprising: a scanner bore divided into at least two modules from among (i) a head module, (ii) a thoracic module, (iii) an abdomen module and (iii) a leg module; for each module of the at least two modules, the modules include: electromagnets situated along an inner wall of the module; a power supply controlled by a controller so as to generate pulses of electric current at a specified frequency and for a specified duration; detectors positioned along the inner wall and configured to detect a reflected signal from tissue of a subject in the scanner bore during a hiatus between the pulses and to transmit the signal to a remote computer system for analysis, wherein each of the at least two modules is configured to independently and simultaneously perform an MRI scan and transmit data regarding a result of the MRI scan to the remote computer system for analysis.

61. The portable assembly of claim 60, wherein the scanner bore is divided into at least three modules from among (i) the head module, (ii) the thoracic module, (iii) the abdominal module and (iv) the legs module.

62. The portable assembly of claim 60, wherein the scanner bore is radially adjustable by one or more of (i) a pneumatic adjustment mechanism and (ii) an electromechanical adjustment mechanism.

63. The portable assembly of claim 60, wherein each of the at least two modules is radially adjustable.

64. The portable assembly of claim 60, further comprising, for each of the at least two modules, at least one of the following adjustment mechanisms:(a) an adjustment mechanism for a radial adjustment of the module comprising a series of pneumatic actuators situated along the inner wall; and(b) a precision adjustment mechanism for the radial adjustment of the module comprising a series of electromechanical actuators situated along the inner wall of the module,SH-MICH-008-PCT wherein a radius of the module is configured to be radially adjusted by the one or more adjustment mechanisms.

65. The portable assembly of claim 60, wherein the power supply comprises piezoelectric crystals and is connected separately and independently to each of the electromagnets.

66. The portable assembly of claim 60, wherein the power supply is a piezoelectric battery configured by the controller to supply electrical impulses to the electromagnets so as to generate a specific amount of power in a controlled sequence.

67. The portable assembly of claim 60, wherein a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

68. A portable assembly for an MRI imaging system, the assembly comprising: a scanner bore having an inner wall; electromagnets positioned along the inner wall, each electromagnet comprising a metallic core surrounded by a coil assembly, the coil assembly comprising one or more coils made of a metal and graphene; a power supply configured to generate pulses of electric current, at a specified frequency and for a specified duration, and an electromagnetic field; detectors positioned along the inner wall and configured to detect a reflected signal from a tissue of a subject inside the scanner bore, and to transmit the signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis, wherein the generated pulses are of a duration of a second or less.

69. The portable assembly of claim 68, wherein each coil of the coil assembly comprises a metal layer, a graphene layer and a ceramic layer.

70. The portable assembly of claim 68, wherein the coil assembly comprises at least two coils and comprises liquid nitrogen situated in a space between adjacent coils of the at least two coils.

71. The portable assembly of claim 68, wherein the liquid nitrogen is at a temperature of minus 185° C or higher.

72. The portable assembly of claim 68, wherein each electromagnet is superconductive.

73. The portable assembly of claim 68, wherein the power supply comprises pyroelectric piezoelectric material and an actuator, the power supply controlled by a controller so as to generate the pulses of electric current at the specified frequency and for the specified duration.SH-MICH-008-PCT74. The portable assembly of claim 68, wherein the duration of the pulses is less than 100 milliseconds.

75. The portable assembly of claim 68, wherein the duration of the pulses is between 3 milliseconds and 333 milliseconds and wherein the number of pulses per second is 3-300.

76. The portable assembly of claim 68, wherein a combination of the electromagnets is not colinear and the reflected signal transmitted to the remote computer system is configured to allow the remote computer system to construct a three-dimensional image.

77. A method of calibrating frequencies for an MRI imaging system, the method comprising: using electromagnets of a coil assembly, connected to an inner wall of a scanner bore, to emit toward a subject a first set of signals at a first frequency that represents a reference frequency for MRI imaging of a particular body portion and processing the first set of signals to generate a first set of images; using the electromagnets to emit toward the subject a second set of signals at a frequency higher than the first frequency and a third set of signals at a frequency lower than the first frequency, and processing the second set of signals and the third set of signals to generate a second set of images and a third set of images; selecting a best set of images from among the second set first image and the third set of images by comparing a quality of the second set of images with a quality of the third set of images, or by comparing the first set of images with each of the second set and the third set of images; emitting a set of one or more signals at an adjusted frequency that was used to generate the best set of images; and determining a final frequency by adjusting the adjusted frequency as many times as necessary to approach a resonance frequency of the subject's tissue being scanned.

78. The method of claim 77, wherein the determining of the final frequency by adjusting the adjusted frequency as many times as necessary to approach the resonance frequency is implemented by comparing as many times as necessary a quality of a set of images generated from a signal emitted at a most current adjusted frequency with a quality of a set of images generated from a signal emitted at a new frequency selected to be higher or lower than the most current adjusted frequency.

79. The method of claim 77, further comprising selecting the new frequency by taking into consideration previously rejected frequencies.SH-MICH-008-PCT80. The method of claim 77, further comprising: using a power supply connected to each of the electromagnets to generate pulses of electric current and an electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration; and using sensors / detectors positioned along the inner wall and configured to detect a signal derived from changes in a tissue of a subject inside the scanner bore, the changes responsive to the electromagnetic field, and to transmit the signal for use by a remote computer system in generating at least one of an image, an analysis and a diagnosis, wherein the generated pulses are of a duration of a second or less.

81. A method of manufacturing ceramic superconductive electromagnets, the method comprising: inputting yttrium barium copper oxide powder and aluminum oxide powder into a 3-D printer; programming the 3-D printer using 3-D printing design software to output a ceramic coil in the form of a tube in which a layer of aluminum oxide surrounds a layer of yttrium barium copper oxide; heating the ceramic coil in an oven at a temperature of at least 300°C for at least 18 hours; and slow cooling the ceramic coil for at least 18 hours.

82. The method of claim 81, further comprising inserting liquid nitrogen into a cavity of the tube of the ceramic coil such that the liquid nitrogen is hermetically sealed.

83. A method of MRI imaging, comprising: scanning a portion of a subject using electromagnets positioned along an inner wall of a scanner bore such that the electromagnets are positioned so as to be colinear and so that the electromagnets emit a signal to tissue of the subject, wherein a reflected signal from the tissue is detected by detectors and transmitted to a computer system to initially construct a three-dimensional image; and converting, by the computer system, the three-dimensional image into a two-dimensional image.

84. The method of claim 83, further comprising outputting, by the computer system, one or more of (i) an analysis of the two-dimensional image and (ii) a diagnosis based on the two-dimensional image.SH-MICH-008-PCT85. The method of claim 83, wherein a quantity of the electromagnets is a number from 16 to 256 and wherein each of the electromagnets comprises a coil assembly.

86. The method of claim 83, further comprising using a power supply connected to each of the electromagnets to generate pulses of electric current and an electromagnetic field, the power supply controlled by a controller so as to generate the pulses of electric current at a specified frequency and for a specified duration, wherein the generated pulses are of a duration of a second or less.

87. The method of claim 83, wherein the computer system is remote and the electromagnets are part of a portable assembly.

88. The method of claim 83, further comprising using the two-dimensional image to determine a precise localization of a defect in the subject's body.

89. The method of claim 88, wherein the defect is in a brain of the subject.

90. A method of MRI imaging, comprising: scanning a portion of a subject using electromagnets positioned along an inner wall of a scanner bore such that the electromagnets are positioned so as to not be coplanar and so that the electromagnets emit a signal to tissue of the subject, wherein a reflected signal from the tissue is detected by detectors and transmitted to a computer system to initially construct a three-dimensional image; and converting, by the computer system, the three-dimensional image into a two-dimensional image.

91. The method of claim 90, further comprising using the two-dimensional image to determine a precise localization of a defect in the subject's body.

Images