This is achieved by a mathematical operation called a Fourier transform.Advances in materials science and engineering have played a central role in the development of classical computers and will undoubtedly be critical in propelling the maturation of quantum information technologies. When using magnetic field gradients, the obtained NMR signal contains different frequencies corresponding to the different tissue spin positions and is called the MRI signal. After sampling, the analog MRI signal is digitized and stored for processing, which consists of a separation of the signal contributions from different spatial locations represented by pixels in the final image. The portion of the gradient coils and the associated current that is perpendicular to the main magnetic field cause a force (Lorentz force) on the coils. The gradients are turned on and off very quickly in this process causing them to vibrate and producing the majority of the acoustic noise during MR image acquisition. Spatial encoding of the MRI signal is accomplished through the use of magnetic field gradients (smaller additional magnetic fields with an intensity that linearly depends on their spatial location): spins from protons in different locations precess at slightly different rates. The contrast in MR images originates from the fact that different tissues have, in general, different T1 and T2 relaxation times as this is especially true for soft tissues, it explains the excellent soft tissue contrast of MRI. Concurrently, the magnetization vector slowly relaxes towards its equilibrium orientation that is parallel to the magnetic field: this occurs with a time constant called the spin-lattice relaxation time (T1). The loss of coherence of the spin system attenuates the NMR signal with a time constant called the transverse relaxation time (T2). ![]() The NMR signal is attenuated due to two simultaneous relaxation processes. When a receiving coil (an electrical conductor) is put in the vicinity of the tissue, the transverse magnetization, that still rotates as the Larmor precession, will generate an electric current in the coil by Faraday induction: this is the nuclear magnetic resonance (NMR) signal. The duration of the RF pulse is chosen such that it tilts the spin magnetization perpendicularly to the magnetic field. When tuned to the Larmor frequency, the RF pulse is at resonance: it creates a phase coherence in the precession of all the proton spins. ![]() Excitationĭuring the image acquisition process, a radiofrequency (RF) pulse is emitted from the scanner. The parallel magnetization scales with the magnetic field intensity, basically at 3 T it will be twice the value obtained at 1.5 T. Additional preparation sequences can also be performed to manipulate the magnetization and so the image contrast, e.g. inversion preparation. The resulting magnetization of all protons inside the tissues aligns parallel to the magnetic field. The spin magnetization vector precesses (rotates) around the magnetic field at a frequency called the Larmor frequency, which is proportional to the magnetic field intensity. The proton, the nucleus of hydrogen, possesses an intrinsic magnetization called spin. In living tissues there are a lot of hydrogen atoms included in water molecules or in many different other molecules. The patient is placed in a static magnetic field produced by the magnet of the MRI scanner. Essentially, the process can be broken down into four parts:įor a more detailed description of each part of the process, please refer to the links scattered throughout this introduction and at the bottom of the page. What follows is a very abbreviated, 'broad strokes' description of the process. ![]() The physics of MRI are complicated and much harder to understand than those underpinning image generation in plain radiography, CT or ultrasound.
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