Patent Description:
Ultra-low radio frequency energy therapy is based on measurement of the unique electrostatic potential of a target molecule. The unique and specific ultra-low radio frequency energy is used to induce electron and charge transfer in a defined bioactive target, altering cell dynamics to produce a therapeutic response. In at least some embodiments, to provide therapy, an ultra-low radio frequency energy cognate of a target molecule is delivered locally and non-systemically via a medical device. To provide the therapy, the ultra-low radio frequency energy cognate must be obtained.

<CIT> describes the identification of molecules using electromagnetic write-heads and magneto-resistive sensors. In one embodiment, an electromagnetic write-head magnetically excites a molecule with an alternating magnetic field. A magneto-resistive sensor measures the resonant response of the magnetically excited molecule. A processor compares the resonant response to a table of known responses of different molecules to identify the chemical composition of the target molecule.

<CIT> describes detection devices, systems, and methods that use magnetic nanoparticles (MNPs) to allow molecules to be identified. Embodiments of this disclosure include magnetic sensors (e.g., magnetoresistive sensors) that can be used to detect temperature-dependent magnetic fields (or changes in magnetic fields) emitted by MNPs, and, specifically to distinguish between the presence and absence of magnetic fields emitted, or not emitted, by MNPs at different temperatures selected to take advantage of knowledge of how the MNPs' magnetic properties change with temperature. Embodiments disclosed herein may be used for nucleic acid sequencing, such as deoxyribonucleic acid (DNA) sequencing.

<CIT> describes a sequencing-by-synthesis (SBS) method that includes providing a detection apparatus that includes an array of magnetically-responsive sensors. Each of the magnetically-responsive sensors is located proximate to a respective designated space to detect a magnetic property therefrom. The detection apparatus also includes a plurality of nucleic acid template strands located within corresponding designated spaces. The method also includes conducting a plurality of SBS events to grow a complementary strand by incorporating nucleotides along each template strand. At least some of the nucleotides are attached to corresponding magnetic particles having respective magnetic properties. Each of the plurality of SBS events includes detecting changes in electrical resistance at the magnetically-responsive sensors caused by the respective magnetic properties of the magnetic particles. The method also includes determining genetic characteristics of the complementary strands based on the detected changes in electrical resistance.

The present invention, inter alia, relates tos a measurement system that includes a container configured to contain solvated target molecules and a plurality of magnetoresistive (MR) sensor devices, each including at least one MR sensor disposed near the container and configured to measure a magnetic field generated by the solvated target molecules, each of the at least one MR sensor including a pin layer having a pinned direction of magnetization, a free layer having a direction of magnetization that varies with an applied magnetic field, and a non-conductive layer separating the pin layer and the free layer, wherein the MR sensor devices are arranged along at least three orthogonal directions with respect to the container.

In at least some embodiments, the plurality of MR sensor devices are arranged in a plane around the container.

In at least some embodiments, each of the at least one sensor device includes a plurality of the MR sensors. In at least some embodiments, the plurality of MR sensors are arranged in a Wheatstone bridge.

The present invention further relates to a method that includes solvating target molecules and placing the solvated target molecules in a container; providing the container with the solvated target molecules in a measurement system including a plurality of magnetoresistive (MR) sensor devices including at least one MR sensor disposed near the container and configured to measure a magnetic field generated by the solvated target molecules, each of the at least one MR sensor including a pin layer having a pinned direction of magnetization, a free layer having a direction of magnetization that varies with an applied magnetic field, and a non-conductive layer separating the pin layer and the free layer, wherein the MR sensor devices are arranged along at least three orthogonal directions with respect to the container; applying a stimulus to the solvated target molecules; using the at least one MR sensor of the at least one MR sensor device to acquire a magnetic field generated by the solvated target molecules in response to the stimulus; and producing signals by the at least one MR sensor of the at least one MR sensor device in response to the acquired magnetic field.

In at least some embodiments, the method further includes amplifying the signals from the at least one MR sensor of the MR sensor devices and converting the amplified signals into digital signals. In at least some embodiments, the method further includes delivering the digital signals to a delivery device to simulate the presence of the solvated target molecule. In at least some embodiments, the method further includes storing the digital signals as a data file in an audio file format.

In at least some embodiments, the plurality of MR sensor devices are arranged in a plane around the container.

The present invention further relates to a therapy delivery system that includes any of the measurement systems described above; a near field magnetic induction (NFMI) transceiver device configured to be worn or otherwise disposed on a patient and configured to utilize the measured magnetic field of the measurement system to produce signals for delivery of therapy, the NFMI transceiver device comprising a NFMI transceiver; and a therapy delivery device including a NFMI receiver configured to receive the signals from the NFMI transceiver device, and a therapy delivery circuit configured to deliver a therapeutic magnetic signal, based, at least in part, on the received signals from the NFMI transceiver device, to the patient when the patient wears the therapy delivery device or has the therapy delivery device disposed on skin of the patient or has the therapy delivery device implanted.

In at least some embodiments, the NFMI transceiver device further includes a communications circuit for communication, other than NFMI, to a user device. In at least some embodiments, the therapy delivery system further comprises the user device configured to communicate with the NFMI transceiver device through the communications circuit of the NFMI transceiver device.

Non-limiting and non-exhaustive embodiments of the present invention are described with reference to the following drawings. In the drawings, like reference numerals refer to like parts throughout the various figures unless otherwise specified.

The present invention is directed to the area of systems and methods for measuring magnetic fields. The present invention is also directed to systems and methods for measuring magnetic fields from solvated target molecules using a magnetoresistive sensor, as well as systems and methods for delivery of therapy using the measured magnetic fields.

The signals for delivery of ultra-low radio frequency energy can be generated from measurements of electromagnetic characteristics of one or more target molecules, such as the unique electrostatic potential of a target molecule. Every molecule has a unique electrostatic surface potential. This potential influences how a molecule interacts with proteins and other biological agents. Electron and charge transfer are central to many biological processes and are a direct result of interacting surface potentials. Artificial electromagnetic fields (e.g., the ultra-low radio frequency energy) are capable of triggering a similar receptor response and conformational change in the absence of a physical drug or molecular agonist.

In at least some embodiments, the unique and specific ultra-low radio frequency energy is used to induce electron and charge transfer in a defined bioactive target, altering cell dynamics to produce a therapeutic response. In at least some embodiments, to provide therapy, an ultra-low radio frequency energy cognate of a target molecule is delivered locally and non-systemically via a delivery device. Pre-clinical and clinical studies suggest that ultra-low radio frequency energy therapy provides the ability to specifically regulate metabolic pathways and replicate known mechanisms of action for proven commercial drugs or other molecules.

Examples of devices and systems for measuring or using ultra-low radio frequency energy can be found in <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; and <CIT>; <CIT> and <CIT>; <CIT>; <CIT>; and <CIT>; <CIT> and <CIT>; and <CIT>.

In at least some embodiments, the delivery of ultra-low radio frequency energy includes the generation of a magnetic field having a field strength of up to <NUM> Gauss, for example, in the range of <NUM> to <NUM>. In at least some embodiments, the delivery of ultra-low radio frequency energy includes the generation of a magnetic field having a field strength of up to <NUM> Gauss. In at least some embodiments, the delivery of ultra-low radio frequency energy includes the generation of a therapeutic magnetic signal having a frequency in the range of <NUM> to <NUM>, in the range of <NUM> to <NUM>, or in the range of <NUM> to <NUM>.

An example of affecting biologic activity with ultra-low radio frequency energy fields includes experiments conducted to demonstrate the specificity and cellular effects of a specific ultra-low radio frequency energy targeting epidermal growth factor receptor, EGFR, on glioblastoma cell line U-<NUM>. At <NUM> and <NUM> hours, EGFR inhibition by the ultra-low radio frequency energy reduced the level of EGFR protein by <NUM>% and <NUM>%, respectively. These data indicate that ultra-low radio frequency energy can inhibit gene expression at the transcriptional and protein levels, similar to what is observed with physical small interfering RNA (siRNA) inhibition. Specific EGFR knockdown effect was detected in U-<NUM> cells treated with ultra-low radio frequency energy using an <NUM> gene PCR-based array. See, "Effects of Magnetic Fields on Biological Systems An Overview"; X. Figueroa, Y. Murray, and M. Butters; EMulate Therapeutics; March <NUM>, <NUM>.

In another example, ultra-low radio frequency energy therapy was provided as a cancer treatment for over <NUM> dogs (pets) with naturally occurring malignancies. Interim review of the first <NUM> pets observed partial responses and complete responses in over <NUM> different tumor types. No clinically important or significant toxicities (Grade <NUM> or <NUM>) were observed.

Conventionally, superconducting quantum interference devices (SQUID) have been used to measure electromagnetic characteristics of molecules, such as the unique electrostatic potential of the molecules. SQUIDs, however, can be bulky, expensive, and require cryogenic fluids for operation.

As described herein, a magnetoresistive (MR) sensor can be used in a single or multi-channel configuration to measure the electromagnetic characteristics of a molecule, such as, for example, the magnetic field of a solvated target molecule, and produce measurement signals. The measurement signals are processed and stored (for example, as a <NUM>-bit WAV file) for uses such as, for example, therapy or drug discovery. In at least some embodiments, the bandwidth of the stored measurement signals is in a range from DC to <NUM> or more. In at least some embodiments, the delivery of ultra-low radio frequency energy includes the generation of a therapeutic magnetic signal having one or more frequencies (or ranges/bands of frequencies) in the range of <NUM> to <NUM>, in the range of <NUM> to <NUM>, or in the range of <NUM> to <NUM>.

In at least some embodiments, the measurement signals can be processed and stored as a data file in audio file format (for example, a WAV, PCM, AIFF, MP3, AAC, WMA, FLAC, ALAC, MIDI, APE, MP2, M4A, AAC, VQF, AMR, AC3, RA, 3GA, OGG, ASF, DSD, or MQA file format, or any other suitable format). Audio file formats may be particularly useful as these formats are used to store multi-frequency information for generating electromagnetic signals. A WAV file is used herein as an example of the data file for storage and delivery of the signals to produce ultra-low radio frequency energy. A suitable resolution can be used including, but not limited to, <NUM>, <NUM>, or <NUM> bit resolution.

In at least some embodiments, the signals for delivery of ultra-low radio frequency energy can be generated from measurements made using one or more particular target molecules. These measurements can be, for example, processed, converted from analog to digital signals, and stored for delivery using any suitable delivery device. The molecule(s) used to obtain the signals can be any suitable drug molecule(s), therapeutic molecule(s), other molecule(s) that produce(s) a physiological or biological response, or the like.

In at least some embodiments, a delivery device for the ultra-low radio frequency energy can use any suitable method of delivery of the signals from the data file including, but not limited to, analog or digital modulation for signal transmission. Any suitable modulation technique can be used including, but not limited to, any type of amplitude, frequency, phase, or other modulation.

<FIG> illustrates one embodiment of a magnetoresistive (MR) sensor <NUM> (which is also known as a tunnel magnetoresistive (TMR) sensor or magnetic tunnel junction (MTJ) sensor) that includes a thin film <NUM> of non-magnetic material between two ferromagnetic films that form a pin layer <NUM> and a free layer <NUM>, respectively. The pin layer <NUM> has a direction of magnetization <NUM> that is pinned. Pinning can be accomplished by a variety of methods including, but not limited to, forming the pin layer <NUM> of a material in a defined crystal structure. The direction of magnetization <NUM> of the free layer <NUM> follows the direction of an external magnetic field. For example, the free layer <NUM> can be formed of a material in an amorphous (e.g., non-crystalline) structure. Examples of MR devices are found in, for example, European Patent Application No. <CIT>.

The electrical resistance of the magnetoresistive sensor <NUM> varies (in at least some embodiments, proportionally) with the relative angle between the directions of magnetization in the pin layer <NUM> and the free layer <NUM>. Thus, by observing the resistance of the magnetoresistive sensor <NUM>, the direction of the external magnetic field, which affects the direction of magnetization <NUM> of the free layer <NUM>, can be determined.

One or more MR sensors <NUM> can be used to measure the magnetic field by coupling to a DC power source. In <FIG>, a MR sensor device <NUM> includes a Wheatstone bridge arrangement <NUM> of four MR sensors <NUM> (where the arrows <NUM> indicate the direction of magnetization of the pin layer <NUM>) can be used for differential temperature compensation. One example of a MR sensor device that utilizes the MR sensors <NUM> is the TDK Nivio xMR Sensor (TDK Corporation, Tokyo, Japan).

<FIG> illustrates one embodiment of a sensor arrangement <NUM> with multiple MR sensor devices <NUM> disposed around a container <NUM> with the target molecule <NUM> solvated in a solvent (for example, water, saline, plasma, or blood). The target molecule <NUM> can be any suitable target including, but not limited to, drug molecules (e.g., Taxol), oligonucleotides (e.g., RNA, mRNA, or the like), or any combination thereof.

In the illustrated embodiment of <FIG>, a different MR sensor device <NUM> is positioned at each of the x, y, and z axes to measure the magnetic field arising from the electrostatic potential of the target molecule. Such measurement may include, for example, injecting noise into the sample in the container and recording the resulting magnetic field, as described in the references cited above. In at least some embodiments, the MR sensor device <NUM> can be a single MR sensor <NUM> or can be multiple MR sensors <NUM> arranged in the bridge illustrated in <FIG> or any other suitable arrangement.

<FIG> illustrates another embodiment of a sensor arrangement <NUM> with multiple MR sensor devices <NUM> disposed around the container <NUM> holding the solvated target molecule. In this particular arrangement, eight MR sensor devices <NUM> are arranged around in the container in the x-y plane. Any other suitable two-dimensional arrangement of multiple (e.g., three, four, six, eight, ten, twelve, or more or any other suitable number) MR sensor devices <NUM> can be used.

<FIG> illustrates a further embodiment of a sensor arrangement <NUM> with multiple (e.g., three, four, six, eight, ten, twelve, or more or any other suitable number) MR sensor devices <NUM> disposed around the container <NUM> with the solvated target molecule. In this particular arrangement, three MR sensor devices <NUM> are arranged around each of the x, y, and z axes. It will be recognized that other three-dimensional arrangements of MR sensor devices (or any other magnetic field sensor devices) can be used including, for example, providing the arrangement illustrated in <FIG> along multiple planes (for example, the x-y plane and the y-z plane).

The arrangements of MR sensor devices <NUM> illustrated in <FIG>, <FIG> are examples of multi-channel configurations for recording electromagnetic characteristics (for example, the electrostatic potential) of a target molecule. It will be understood that single channel configurations with a single MR sensor device (or multiple MR sensor devices positioned together) can also be used.

<FIG> illustrates the sensor arrangement <NUM> disposed within a shield <NUM> to reduce or remove the ambient magnetic field (such as the Earth's magnetic field) within the shield. The shield can be a passive shield (for example, made of mu-metal or other shielding material or a Faraday cage or the like) or an active shield (for example, one or more magnetic field generators to counter the ambient magnetic field) or any combination thereof.

<FIG> is a flowchart of one embodiment of a workflow for generating and employing ultra-low radio frequency energy using the MR sensor devices described herein (or any other suitable magnetic field sensors. ) In step <NUM>, the target molecule is solvated in a solvent, such as, for example, water, saline, plasma, or blood. In step <NUM>, the solvated target is placed in a MR sensor arrangement, such as one of the arrangements illustrated in <FIG>, <FIG>, or any other multi-channel or single channel configuration or arrangement. Optionally, a DC offset field (e.g., a voltage difference) can be applied to the solvated target to align the molecules along a particular direction defined by the DC offset field.

In step <NUM>, in at least some embodiments, the solvated target is subjected to a stimulus (for example, noise or other suitable signal) to elicit a response. Optionally, white noise can be injected to enhance the response.

In step <NUM>, the MR sensor devices of the MR sensor arrangement acquires the magnetic field generated by the solvated target. The MR sensor devices generate signals based on the acquired magnetic field.

In step <NUM>, the signals from the MR sensor devices are amplified or otherwise processed, converted from analog to digital signals, and stored. In at least some embodiments, the signals can be processed using auto- or cross-correlations. Any other suitable signal processing techniques can be used.

In step <NUM>, the stored digital signals are then provided to a delivery device, such as a therapy delivery device, to deliver the signals to a target and elicit the desired response based on the initial target molecule. In at least some embodiments, the delivery of ultra-low radio frequency energy includes the generation of a magnetic field having a field strength of up to <NUM> Gauss.

<FIG> illustrates one embodiment of a measurement and signal processing system. The system includes any suitable sensor arrangement <NUM> (with, or capable of receiving, the solvated target molecule <NUM> in a container <NUM>, as illustrated in <FIG>) and a computing arrangement <NUM> for directing and receiving the measurements of the sensor arrangement. The computing arrangement <NUM> includes at least one processor <NUM> for directing the measuring, obtaining signals from the sensor arrangement, and processing the signals and at least one memory <NUM> for storing instructions for the processor and for storing the signals or the processed signals (for example, as a data file that is optionally in an audio file format. ) Any suitable processor <NUM> can be used including, but not limited to, microprocessors, application specific integrated circuits (ASICs), other integrated circuits, or the like or any combination thereof. Any suitable memory <NUM> can be used including, but not limited to, RAM, ROM, EEPROM, flash memory, or the like or any combination thereof. The processor <NUM> or the memory <NUM> (or both) can be local or non-local to the sensor arrangement or can be distributed.

A variety of therapy delivery devices and therapy delivery systems can be used to deliver ultra-low radio frequency energy that based on the measurements or signals obtained using the MR sensor devices (or any other suitable magnetic field sensors), as described above. In at least some embodiments, a therapy delivery system can utilize NFMI to communicate with, and optionally control, one or more therapy delivery devices or sensors or any combination thereof. Near Field Magnetic Induction (NFMI) is a short-range wireless communication technology that utilizes magnetic fields for inductive transmission between coils or transducers in individual devices, in contrast to many conventional communications techniques that utilize electrical transmission through antennas. In at least some embodiments, NFMI can be superior to electrical/antenna transmission technologies for body-area networks, such as WBAN, because NFMI is attenuated less by the body than many electrical/antenna transmission technologies. Also, NFMI signals are attenuated more strongly over distance (in at least some cases, approximately by a factor of <NUM>/r<NUM> where r is distance) than a number of other conventional transmission technologies and, therefore, NFMI may provide a more private network that is substantially limited to the body of the patient. This can reduce interference or privacy breaches. In at least some embodiments, NFMI is more power efficient than other wireless technologies such as Bluetooth™, near field communication (NFC), or the like and may have lower power consumption than these technologies for transmitting the same data or signals. In addition to communication using NFMI, in at least some embodiments, the same coils can be used for wireless charging of device batteries or other power sources using magnetic induction.

<FIG> illustrates one embodiment of a therapy delivery system <NUM> that includes a NFMI transceiver device <NUM> (NT) and one or more system devices <NUM> that can be therapy delivery devices (for example, devices T1, T2, T3, IT1, and IT2), sensors (for example, sensors S1, S2, and IS1), or the like or any combination thereof. Examples of sensors include, but are not limited to, the magnetoresistive sensor <NUM> (<FIG>) or MR sensor devices <NUM> (<FIG>); temperature sensors such as thermistors or infrared sensors; piezoelectric or other pressure sensors (to measure, for example, blood pressure, pulse rate, inhalation/expiration, or other physical parameters); fluid sensors such as sweat sensors or blood sensors (for example, glucose sensors); pH sensors; cameras; microphones; healing detection sensors; or the like or any combination thereof.

The therapy delivery system <NUM> can optionally include one or more user devices <NUM> (UD) which may be, for example, a mobile device (such as a mobile phone, tablet, laptop, personal data assistant, or the like), a computer (for example, a laptop, a desktop computer, a server, or the like), a dedicated programming or monitoring device, or the like or any combination thereof. A user device <NUM> can, for example, direct operation of, or control, the NFMI transceiver device <NUM> or one or more of the system device <NUM> or any combination thereof; program the NFMI transceiver device <NUM> or one or more of the system device <NUM> or any combination thereof; process or analyze data from any of the system devices <NUM>; transmit data or other information to other devices, such as a computer or server at a healthcare facility; provide information to a user or patient on a screen of the user device <NUM>; or the like or any combination thereof. In at least some embodiments, the delivery of therapy or the programming or alteration of therapy parameters may be restricted to a user with credentials, such as a password or other identification. The user device <NUM> may include one or more programs, applications, or features that provide these functions. In at least some embodiments, the NFMI transceiver device <NUM> can also perform one or more of these functions of a user device <NUM>.

As also illustrated in <FIG>, the therapy delivery system <NUM> can optionally include a sensor arrangement (SA) <NUM> (or one or more MR sensor devices <NUM>, <NUM>) to acquire or measure the magnetic field to produce signals that will be processed or otherwise used for the therapy as described above. In at least some embodiments, the sensor arrangement <NUM> is coupled directly to the NFMI transceiver device <NUM> or the user device <NUM> or both. It will be understood that the sensor arrangement <NUM> may also not be part of the therapy delivery system <NUM>, but may be an independent system for measuring a magnetic field, as described above, and signals arising from the measurement of the magnetic field can then be processed, stored, distributed, or otherwise provided to the therapy delivery system <NUM> (e.g., to the NFMI transceiver device <NUM>, the user device <NUM>, the therapy deliver devices (for example, devices T1, T2, T3, IT1, and IT2), or any combination thereof.

The NFMI transceiver device <NUM> communicates with the one or more system devices <NUM> by NFMI. In at least some embodiments, the NFMI transceiver device <NUM> and one or more system devices <NUM> create a Wireless Body Area Network (WBAN) with NFMI transmission. The development of new sensors and therapy delivery devices, as well as miniaturization of previously developed sensors and therapy delivery devices, provides an opportunity for monitoring of health conditions of patients. Such monitoring may be continuous or periodic and may be available at home or elsewhere, instead of being relegated to a healthcare facility. The use of wireless connectivity technologies can facilitate operation of, and data collection from, sensors and therapy delivery devices. The creation of a single body central gateway, such as a Wireless Body Area Network (WBAN), to transmit or receive from one or more therapy delivery devices or sensors can enhance this operation and data collection. The use of a WBAN can facilitate the collection of data for patient treatment of diseases or disorders, such as, for example, chronic diseases, like diabetes mellitus, cardiovascular diseases, respiratory diseases, cancer, other serious diseases, or the like. In at least some embodiments, data can be further exchanged between the patient and a healthcare provider (for example, a doctor, surgeon, clinic, hospital, or the like or any combination thereof). Such exchanges may facilitate mobile health (mHealth) or Telehealth services and applications.

In at least some embodiments, the NFMI transceiver device <NUM> can be worn or carried by the patient. Each of the system devices <NUM> can be independently disposed on the patient, worn by the patient, or implanted in the patient. Devices <NUM> labeled IS1 and IT1/IT2 are an implanted sensor and implanted therapy devices, respectively. <FIG> illustrates one example of a NFMI transceiver device <NUM> worn by the patient <NUM> and a therapy delivery device 804a positioned on the patient.

<FIG> schematically illustrates NFMI transmission of an input signal <NUM> by magnetic field induction from a transmitting coil <NUM> (for example, in a NFMI transceiver <NUM>) to a receiving coil <NUM> (for example, in a system device <NUM>) to produce an output signal <NUM>. As an alternative to the transmitting coil <NUM> or receiving coil <NUM> and other suitable transducer can be used that facilitates NFMI transmission/reception. The use of the term "coil" herein includes other suitable transducers unless indicated otherwise.

NFMI can use any type of analog or digital modulation for signal transmission including, but not limited to, any type of amplitude, frequency, phase, or other modulation. In at least some embodiments, the same coils <NUM>, <NUM> can be used for transferring power to a device by magnetic induction. In other embodiments, different coils or antennas may be used for transferring power to the device. In at least some embodiments, the transmitting coil <NUM> and receiving coil <NUM>, and associated circuitry, can both transmit and receive so that the NFMI transceiver device <NUM> and system devices <NUM> can communicate in both directions using NFMI.

Returning to <FIG>, in at least some embodiments, the NFMI transceiver device <NUM> can communicate with one or more user devices <NUM> or the sensor arrangement <NUM> using any suitable communications arrangement or protocol including, but not limited to, NFMI, Bluetooth™, near field communications (NFC), wireless fidelity (WiFi), satellite communication, cellular communication, Infrared Data Association standard (IrDA), or the like or any combination thereof. In some embodiments, the NFMI transceiver device <NUM> communicates with at least one user device <NUM> directly. In some embodiments, the NFMI transceiver device <NUM> communicates with at least one user device <NUM> through a network such as, for example, a personal area network (PAN), local area network (LAN), metropolitan area network (MAN), wide area network (WAN), cellular network, the Internet, or any combination thereof. In some embodiments, the NFMI transceiver device <NUM> communicates to a user device <NUM> through another user device <NUM>. For example, the NFMI transceiver device <NUM> may communicate (using, for example, Bluetooth™ or NFC) with a patient's mobile phone (acting as a user device <NUM>) and the patient's mobile phone may communicate (using, for example, cellular communications or WiFi over the Internet or other network or combination of networks) with a server or computer (acting as another user device <NUM>) at a healthcare facility (such as a hospital, clinic, or doctor's office).

<FIG> is a functional block diagram of one embodiment of a NFMI transceiver device <NUM>, one embodiment of a therapy delivery device 804a, and one embodiment of a sensor device 804b. Other embodiments of these devices may include more or fewer components than those illustrated in <FIG>.

The NFMI transceiver device <NUM> includes a NFMI coil/transceiver circuit <NUM> (i.e., a NFMI transceiver), a processor <NUM>, a memory <NUM>, a power source <NUM> (for example, a battery), an optional communications antenna/circuit <NUM> for communication with a user device <NUM> (<FIG>), and an optional power transfer/charging circuit <NUM> for transferring power to a therapy delivery device 804a or sensor device 804b. In some embodiments, the optional communications antenna/circuit <NUM> provides for communication to a user device <NUM> (<FIG>) and can be selected from any suitable communications technique including, but not limited to, Bluetooth™, near field communications (NFC), wireless fidelity (WiFi), satellite communication, cellular communication, Infrared Data Association standard (IrDA), or the like or any combination thereof. In some embodiments, the NFMI transceiver device <NUM> may communicate with a user device <NUM> using NFMI.

The therapy delivery device 804a includes a NFMI coil/transceiver circuit <NUM> (i.e., a NFMI transceiver) or, alternatively, a NFMI coil/receiver circuit (i.e., a NFMI receiver), a therapy delivery circuit <NUM>, an optional processor <NUM>, an optional memory <NUM>, an optional power source <NUM> (for example, a battery), and an optional power transfer/charging circuit <NUM> for receiving power from the NFMI transceiver device <NUM> or other power source. The NFMI coil/transceiver circuit <NUM> (or NFMI coil/receiver circuit) receives signals from the NFMI transceiver device.

The sensor device 804b includes a NFMI coil/transceiver circuit <NUM> (i.e., a NFMI transceiver) or, alternatively, a NFMI coil/transmitter circuit (i.e., a NFMI transmitter), a sensor circuit <NUM>, an optional processor <NUM>, an optional memory <NUM>, an optional power source <NUM> (for example, a battery), and an optional power transfer/charging circuit <NUM> for receiving power from the NFMI transceiver device <NUM> or other power source. The sensor circuit <NUM> of the sensor device 804b will depend on the type of sensor that is used. Examples of types of sensors are listed above. The sensor circuit <NUM> produces sensor signals based on observation of the patient. These sensor signals may be raw output of the sensor or may be processed (for example, using the processor <NUM> or other processing circuitry) to produce modified output of the sensor or even data based on the raw output of the sensor. The NFMI coil/transceiver circuit <NUM> (or NFMI coil/transmitter circuit) transmits the sensor signals to the NFMI transceiver device.

The NFMI coil/transceiver circuit <NUM>, <NUM>, <NUM> include a coil <NUM> (<FIG>) and associated circuitry for transmitting or receiving (or both transmitting and receiving) a signal using magnetic induction to/from a NFMI transceiver device, a therapy delivery device 804a, a sensor device 804b, or a user device <NUM> (<FIG>). Any suitable coil and transceiver (or transmitter or receiver) circuit can be used. Examples of coils and transceiver circuits for NFMI transmitting and receiving are known. Examples of NFMI devices include, but are not limited to, those described in <CIT>; <CIT>; <CIT>; <CIT>; <CIT>; and <CIT>.

The power source <NUM>, <NUM>, <NUM> can be any suitable power source including, but not limited to, batteries, power cells, or the like or any combination thereof. In at least some embodiments, the power source is rechargeable. In at least some embodiments, the NFMI transceiver device <NUM> includes a power transfer/charging circuit <NUM> that can be used to charge a power source <NUM>, <NUM> in the therapy delivery device 804a or sensor device 804b. In at least some embodiments, the power transfer/charging circuit <NUM> may utilize coil of the NFMI coil/transceiver circuit <NUM> to deliver power to the therapy delivery device 804a or sensor device 804b. In at least some embodiments, the NFMI coil/transceiver circuit <NUM>, <NUM> of the therapy delivery device 804a or sensor device 804b can receive the power and deliver to the power transfer/charging circuit <NUM>, <NUM>. In other embodiments, a separate antenna or coil in the power transfer/charging circuit <NUM> may be used to deliver the power to the power transfer/charging circuit <NUM>, <NUM> of the therapy delivery device 804a or sensor device 804b for charging the power source <NUM>, <NUM>. In at least some embodiments, a separate charger (not shown) may be used to the charge the power source <NUM>, <NUM> in the therapy delivery device 804a or sensor device 804b. In at least some embodiments, the power source <NUM> of the NFMI transceiver <NUM> may be charged wirelessly or through a wired connection (for example, by attaching a charging cord to a charging port of the NFMI transceiver).

In other embodiments, a therapy delivery device 804a or sensor device 804b may not have a dedicated power source and the NFMI transceiver device <NUM> (or other device) may deliver power for operation of the therapy delivery device or sensor through the power transfer/charging circuits <NUM>, <NUM>, <NUM> which may utilize the NFMI coil/transceiver circuits <NUM>, <NUM>, <NUM>.

Any suitable processor <NUM>, <NUM>, <NUM> can be used including, but not limited to, microprocessors, application specific integrated circuits (ASICs), other integrated circuits, or the like or any combination thereof. Any suitable memory <NUM>, <NUM>, <NUM> can be used including, but not limited to, RAM, ROM, EEPROM, flash memory, or the like or any combination thereof.

The processor <NUM> can be optional in the therapy delivery device 804a. For example, a processor <NUM> may be optional if the NFMI signal received by the therapy delivery device 804a produces the desired therapy signal in the therapy delivery circuit <NUM>. In other embodiments, the processor <NUM> in the therapy delivery device 804a can be programmed or otherwise operated using the NFMI signal from the NFMI transceiver device <NUM> to deliver, or modify delivery of, therapy using the therapy delivery circuit <NUM>. For example, the NFMI signal from the NFMI transceiver device <NUM> may include new or updated parameters for therapy delivery, initiate therapy delivery, halt therapy delivery, or the like or any combination thereof. Examples of parameters for therapy delivery include, but are not limited to, amplitude, frequency, or, if pulsed, pulsewidth, pulse duration, or pulse parameter.

The processor <NUM> may be optional in the sensor device 804b. For example, a processor <NUM> may be optional if the signal from the sensor circuit <NUM> can be transmitted to the NFMI transceiver <NUM> for processing. In other embodiments, the processor <NUM> in the sensor device 804b can be programmed or otherwise operated using the NFMI signal from the NFMI transceiver device <NUM> to operate, or modify operation of, the sensor 804b. The processor <NUM> may also process, partially or fully, signals from the sensor circuit <NUM> to produce data or signals that are transmitted to the NFMI transceiver device <NUM>. Other processors in the NFMI transceiver device <NUM> or the user device <NUM> (or other devices) may fully or partially process data or signals transmitted form the sensor device 804b.

The therapy delivery device 804a includes a therapy delivery circuit <NUM>. Any suitable therapy delivery circuit <NUM> can be used. In at least some embodiments, at least one of the therapy delivery devices 804a has a therapy delivery circuit that generates ultra-low radio frequency energy. In at least some embodiments, the delivery of ultra-low radio frequency energy can be a therapeutic delivery. In at least some embodiments, the therapeutic delivery can be for the treatment of cancer or other diseases or disorder.

The therapy delivery circuit <NUM> can include, for example, a signal generator <NUM> (<FIG>) to produce a therapeutic magnetic signal, such as a therapeutic signal for ultra-low radio frequency energy. The therapy delivery circuit <NUM> can also include a transducer <NUM> (<FIG>), for example, a coil or antenna, to deliver the therapeutic magnetic signal to the patient.

<FIG> illustrate one embodiment of a therapy delivery device 1204a that includes a NFMI coil/transceiver circuit <NUM>, a therapy delivery circuit <NUM> for delivery of a magnetic therapeutic signal such as an ultra-low radio frequency energy signal, a battery <NUM> (as a power source), and an optional charging circuit <NUM>. These elements of the therapy delivery device 1204a are disposed on a substrate <NUM> which can be, for example, a flex circuit substrate or any other suitable flexible substrate. In some embodiments, the substrate <NUM> can include an adhesive <NUM> disposed on a back surface <NUM> of the substrate to adhere the therapy delivery device 1204a to the skin of the patient, similar to an adhesive bandage. In at least some embodiments, the therapy delivery device 1204a may be otherwise attached to the skin of the patient (e.g., using tape or a bandage) or worn by the patient at or near the treatment site. Optionally, a top substate <NUM> can be disposed over the substrate <NUM> and the components listed above to provide protection to those components.

<FIG> illustrates one embodiment of a NFMI transceiver device <NUM> with some optional features such as a display <NUM>, one or more buttons <NUM> or other input devices (such as a keyboard), and one or more lights <NUM>. In at least some embodiments, the display <NUM> may display instructions or information about operation or warnings or the like or any combination thereof. In at least some embodiments, the lights <NUM> may indicate that the NFMI transceiver device is on/off <NUM>, the status of system devices <NUM>, the status of a power source, warnings about low power source or loss of signal or the like or any combination thereof.

In at least some embodiments, the one or more buttons <NUM> or other input devices may be used by the patient or other user to direct delivery of therapy or alter therapy parameters or the like or any combination thereof. In at least some embodiments, the delivery of therapy or the alteration of therapy parameters may be restricted to a user with credentials, such as a password or other identification.

In at least some embodiments, the use of NFMI for communication between the NFMI transceiver device and the system devices can enable wireless (e.g., cable free) wearable therapy delivery devices for ultra-low radio frequency energy. In at least some embodiments, the use of NFMI for communication between the NFMI transceiver device and the system devices can enable real-time communication with wearable and implantable therapy delivery devices for ultra-low radio frequency energy. In at least some embodiments, the use of NFMI for communication between the NFMI transceiver device and the system devices can enable relatively low attenuation of communication (into the body of the patient) with implantable therapy delivery devices for ultra-low radio frequency energy.

In at least some embodiments, the use of NFMI for communication between the NFMI transceiver device and the system devices can enable simultaneous operation of a therapy delivery device for ultra-low radio frequency energy and at least one sensor device. In at least some embodiments, the use of NFMI for communication between the NFMI transceiver device and the system devices can enable wireless power transfer to a wearable or implantable therapy delivery device for ultra-low radio frequency energy. In at least some embodiments, the use of NFMI for communication between the NFMI transceiver device and the system devices can enable security of signals between the NFMI transceiver device and the system devices.

In at least some embodiments, the present systems can enable simultaneous communication with a user device or sensor arrangement using Bluetooth™ or other communication techniques. Such communication may allow a user to control the NFMI transceiver device and one or more therapy delivery devices for ultra-low radio frequency energy (and, optionally, one or more sensor devices.

Claim 1:
A measurement system, comprising:
a container (<NUM>) configured to contain solvated target molecules (<NUM>); and
a plurality of magnetoresistive , MR, sensor devices (<NUM>, <NUM>), each of the MR sensor devices comprising at least one MR sensor (<NUM>) disposed near the container and configured to measure a magnetic field generated by the solvated target molecules, each of the at least one MR sensor comprising a pin layer (<NUM>) having a pinned direction of magnetization (<NUM>), a free layer (<NUM>) having a direction of magnetization (<NUM>) that varies with an applied magnetic field, and a non-conductive layer (<NUM>) separating the pin layer and the free layer, characterized in that the MR
sensor devices are arranged along at least three orthogonal directions with respect to the container.