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NUCLEAR MAGNETIC RESONANCE IMAGING DEVICE, NUCLEAR MAGNETIC RESONANCE IMAGING METHOD, AND PROGRAM NEW

外国特許コード F210010293
整理番号 (S2019-0244-N0)
掲載日 2021年1月28日
出願国 世界知的所有権機関(WIPO)
国際出願番号 2020JP019524
国際公開番号 WO 2020235505
国際出願日 令和2年5月15日(2020.5.15)
国際公開日 令和2年11月26日(2020.11.26)
優先権データ
  • 特願2019-093569 (2019.5.17) JP
発明の名称 (英語) NUCLEAR MAGNETIC RESONANCE IMAGING DEVICE, NUCLEAR MAGNETIC RESONANCE IMAGING METHOD, AND PROGRAM NEW
発明の概要(英語) A nuclear magnetic resonance imaging device (100) comprises: a magnetostatic coil (10); a holding unit (2); a pulse application unit (30); a reception unit (40); and an image generation unit (51b). The pulse application unit (30) applies a target with a pulse sequence of which echo peak appears before a half of a signal acquisition time from application of a frequency encoding gradient magnetic field for rephasing an NMR signal. The reception unit (40) detects an NMR signal over the entire range from the application of the frequency encoding gradient magnetic field for rephasing the NMR signal to the lapse of the signal acquisition time. The image generation unit (51b) generates an image from the entire NMR signal detected over the above-mentioned entire range.
従来技術、競合技術の概要(英語) BACKGROUND ART
Nuclear magnetic resonance imaging (MRI) refers to acquiring, as a nuclear magnetic resonance (NMR) signal, an induced current generated in a receiving coil by irradiating a subject in a static magnetic field with a specific RF (Radio Frequency) pulse (excitation pulse) while applying a specific gradient magnetic field to cause specific atoms in the subject to nuclear magnetic resonance; An image (of a subject, for example, a two-dimensional image (, that is, a cross-sectional image) and a three-dimensional image) are generated from this signal. NMR signals to which positional information has been added by the application of gradient magnetic fields measured by MRI or the like are also referred to as MRI signals in particular. Also, a set of RF pulses and gradient fields applied at a particular intensity and timing to acquire NMR signals is referred to as a pulse sequence.
The gradient magnetic fields link the real space in which the subject is placed and the spatial frequency space (k-space) of the subject with a Fourier transform relationship, and the MRI signals reflect the information of the k-space of the subject. Thus, in MRI, information on the k-space of the subject is discretely collected from an MRI signal, and discrete inverse Fourier transform is performed on the obtained discrete data to reconstruct an image of the subject in the real space.
Methods of acquiring k-space data from MRI signals include: a method of extracting data on gridpoints in a Cartesian coordinate system of k-space of a subject line by controlling the X-axis, Y-axis, and Z-axis) with tri-axial gradient coils (,); A method (for extracting data in a polar coordinate system in k-space of a subject in order along a plurality of radial straight lines or spiral curves passing through an origin, a radial scan/spiral scan), and the like have been put into practical use.
The MRI signal has a convex, strong signal strength portion generated by manipulation of gradient magnetic fields by a designed pulse sequence, which is referred to as echo. Echo and signal changes before and after the echo include spatial information of the subject. Echoes resulting from the application of gradient magnetic fields are referred to as gradient echoes (gradient echo). Echoes resulting from continued application (of high-frequency magnetic fields, e.g., application) of inverted pulses after application of excitation pulses, are referred to as spin echoes (spin echo). Regardless of the cause of echo, the time from the application of the excitation pulse to the occurrence of echo is referred to as echo time (TE).
Because the NMR nuclei of the target in the subject vary in distribution, density, and relaxation times depending on the circumstances in which they are placed, research and development of MRI signal integration methods (suitable for the target, particularly pulse sequences), have been advanced increasingly.
For example, a partial echo (partial echo) method is known as one such method. In the partial echo method, TE is shortened in the gradient echo (GRE) method, and an MRI signal is acquired until half of a signal acquisition time ta elapses from TE so as to acquire data corresponding to approximately half of the k-space, and The remaining portion of the k-space data is appropriately corrected (, for example, 0-fill (variables), and complemented) by replication based on hemi-symmetry, and then an inverse Fourier transform is performed to generate an MRI image. Fig.5 illustrates a pulse sequence in a case where the partial echo method is applied to the GRE method. For example, PTL 1 discloses an example in which correction is performed with zero fill.
  • 出願人(英語)
  • ※2012年7月以前掲載分については米国以外のすべての指定国
  • NIIGATA UNIVERSITY
  • 発明者(英語)
  • HAISHI Tomoyuki
  • KASEDA Ryohei
  • SASAKI Susumu
国際特許分類(IPC)
指定国 National States: AE AG AL AM AO AT AU AZ BA BB BG BH BN BR BW BY BZ CA CH CL CN CO CR CU CZ DE DJ DK DM DO DZ EC EE EG ES FI GB GD GE GH GM GT HN HR HU ID IL IN IR IS JO JP KE KG KH KN KP KR KW KZ LA LC LK LR LS LU LY MA MD ME MG MK MN MW MX MY MZ NA NG NI NO NZ OM PA PE PG PH PL PT QA RO RS RU RW SA SC SD SE SG SK SL ST SV SY TH TJ TM TN TR TT TZ UA UG US UZ VC VN WS ZA ZM ZW
ARIPO: BW GH GM KE LR LS MW MZ NA RW SD SL ST SZ TZ UG ZM ZW
EAPO: AM AZ BY KG KZ RU TJ TM
EPO: AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR
OAPI: BF BJ CF CG CI CM GA GN GQ GW KM ML MR NE SN TD TG
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