NMR images were obtained from the proton spin noise signals of a water-containing phantom, which was placed in the highly tuned, low-noise resonant circuit of a cryogenically cooled NMR probe in the presence of systematically varied magnetic field gradients. The spatially resolved proton spin density was obtained from the raw signal by a modified projection-reconstruction protocol. Although spin noise imaging is inherently less sensitive than conventional magnetic resonance imaging, it affords an entirely noninvasive visualization of the interior of opaque objects or subjects. Thus, tomography becomes possible even when neither x-ray nor radio frequency radiation can be applied for technical or safety reasons.magnetic resonance imaging ͉ radiation-free imaging ͉ sensitivity M RI is a powerful noninvasive tomographic technique. In medicine MRI is used as a versatile diagnostic tool offering superior contrast of soft tissue in the interior of the human body (1, 2). In addition, MRI is an important methodology in biological and material sciences (3). In conventional MRI, the subjects are placed in a uniform static magnetic field B 0 and irradiated with a series of high-power radio frequency (rf) pulses to excite coherent superpositions of spin states. Rapidly switched, spatially dependent magnetic fields (1, 2) are used to encode the spatial coordinates in the phases of the coherent states. These states induce a detectable signal in an rf coil arranged perpendicularly to the static magnetic field. The resonance frequencies can then be mapped to locations in space. One-dimensional profiles may be acquired quasicontinuously, and experiments with various magnetic field gradients along orthogonal axes are required to obtain two-and threedimensional information. Either two-and three-dimensional Fourier transformation (3) or projection-reconstruction algorithms (4) are generally used to produce the images, in which the signal amplitude at particular frequency coordinates is proportional to the spin density at the corresponding location.The major portion of the rf power applied in MRI and NMR spectroscopy (through, e.g., excitation pulses, refocusing pulses, and decoupling) is deposited within the sample as a result of resistive losses (5). Notwithstanding the potential direct effects of rf irradiation on living cells or tissue (6, 7), the primary biological effect is heating due to the thermogenic properties of the electromagnetic field. Therefore, safety regulations have been established for medical applications of MRI (8, 9) limiting the energy deposition in patients and medical staff. The working frequency o of MRI is linearly proportional to the applied magnetic field B 0 , as given by the Larmor equation: v 0 ϭ ␥B 0 ͞2, where ␥ is the magnetogyric ratio of the observed nucleus ( 1 H for most applications). Although MRI at higher fields provides better sensitivity and better resolution, the rf power deposited in a dielectric sample increases approximately with the second power of the magnetic field and the second pow...