A magnetoencephalography (MEG) apparatus comprising a helmet shaped and configured to fit a range of human head sizes and/or shapes, the helmet comprising a plurality of openings disposed in predetermined locations around the helmet, each opening being adapted to receive a magnetoencephalography field sensor in an arrangement such that the magnetoencephalography field sensor is moveable in a direction towards or away from a human head inside the helmet

A magnetoencephalography (MEG) apparatus comprising a helmet shaped and configured to fit a range of human head sizes and/or shapes, the helmet comprising a plurality of openings disposed in predetermined locations around the helmet, each opening being adapted to receive a magnetoencephalography field sensor in an arrangement such that the magnetoencephalography field sensor is moveable in a direction towards or away from a human head inside the helmet

Various embodiments comprise a magnetic field compensation system. In some examples, the system comprises one or more coil drivers, magnetic field coils, and one or more magnetic field sensors. The one or more coil drivers supply a current to the magnetic field coils to generate a magnetic field. The magnetic field coils receive the current and generate the magnetic field. The magnetic field coils may be arranged in an array. The magnetic field coils individually comprise at least one coil trace pattern that encloses an area. The one or more magnetic field sensors measure the magnetic field generated by the magnetic field coils at a location proximate to the magnetic field coils.

A magnetic field measurement system includes a magnetometer having at least one vapor cell, at least one light source to direct at least two light beams through the vapor cell(s), and at least one detector; at least one magnetic field generator to modify an external magnetic field experienced by the vapor cell(s); and at least one processor configured for: applying a first modulation pattern, b.sub.mod(t), to the magnetic field generator(s) to modulate a magnetic field at the vapor cell(s), where b.sub.mod(t)=[c.sub.x cos(ωt)+s.sub.x sin(ωt), c.sub.y cos(ωt)+s.sub.y sin(ωt), c.sub.z cos(ωt)+s.sub.z sin(ωt)], where c.sub.x, s.sub.x, c.sub.y, s.sub.y, c.sub.z, and s.sub.z are amplitudes and ω is a frequency; directing the light source(s) to direct the light beams through the vapor cell(s); receiving signals from the detector(s); and determining three orthogonal components of the external magnetic field using the received signals. Multi-frequency modulation patterns can alternatively be used.

A brain measurement apparatus configured to generate an MR image and a brain's magnetic field distribution of a subject includes: an MRI module having a transmission coil configured to transmit a transmission pulse toward the subject and a detection coil configured to detect a nuclear magnetic resonance signal generated in the subject by the transmission pulse; an optically pumped magnetometer configured to detect a brain's magnetic field of the subject; a generator configured to generate the MR image based on the nuclear magnetic resonance signal detected by the detection coil and generating the brain's magnetic field distribution based on the brain's magnetic field detected by the optically pumped magnetometer; a marker displayed on the MR image generated by the generator; and a helmet-type frame to which the detection coil, the optically pumped magnetometer, and the marker are attached and which is attached to a head of the subject.

A brain measurement apparatus configured to generate an MR image and a brain's magnetic field distribution of a subject includes: an MRI module having a transmission coil configured to transmit a transmission pulse toward the subject and a detection coil configured to detect a nuclear magnetic resonance signal generated in the subject by the transmission pulse; an optically pumped magnetometer configured to detect a brain's magnetic field of the subject; a generator configured to generate the MR image based on the nuclear magnetic resonance signal detected by the detection coil and generating the brain's magnetic field distribution based on the brain's magnetic field detected by the optically pumped magnetometer; a marker displayed on the MR image generated by the generator; and a helmet-type frame to which the detection coil, the optically pumped magnetometer, and the marker are attached and which is attached to a head of the subject.

Abnormalities in electromagnetic fields in the heart, brain, and stomach, among other organs and tissues of the human body, can be indicative of serious health conditions. Described herein are methods, software, systems and devices for detecting the presence of an abnormality in an organ or tissue of a subject by analysis of the electromagnetic fields generated by the organ or tissue.

Abnormalities in electromagnetic fields in the heart, brain, and stomach, among other organs and tissues of the human body, can be indicative of serious health conditions. Described herein are methods, software, systems and devices for detecting the presence of an abnormality in an organ or tissue of a subject by analysis of the electromagnetic fields generated by the organ or tissue.

An illustrative system includes a brain interface system configured to be worn by a user and to output brain measurement data representative of brain activity of the user while the user is engaged in an electronic messaging session provided by an electronic messaging platform and a computing device configured to obtain the brain measurement data, determine, based on the brain measurement data, a graphical emotion symbol representative of a mental state of the user while the user is engaged in the electronic messaging session, and provide the graphical emotion symbol for use during the electronic messaging session.

The subject of the invention is a method for calibrating a direct neural interface. The calibration is performed by considering a so-called input calibration tensor, formed on the basis of measured electrophysiological signals and so-called output calibration tensor, formed on the basis of measured output signals. The method comprises the application of a least squares multivariate regression implemented by considering a covariance tensor and a cross-covariance tensor which are established on the basis of input and output calibration tensors corresponding to a current calibration period. The method takes into account covariance and cross-covariance tensors established during an earlier calibration period prior to the current calibration period, these tensors being weighted by a forget factor.