Magnetic resonance elastography (MRE) of the liver has been acquired imaging data using a single passive driver placed at the level of the xiphoid process [1]. However, the low amplitude wave image caused poor MRE imaging, i.e., inaccurate shear stiffness value. The frequency level that the mechanical actuator motion reaches at one region is important [2]. This is especially true, because uniformizing the frequency of several biological systems, e.g., heart, lung, limb, and stomach present around liver, is more difficult.To improve the non-uniformity of shear stiffness derived from MRE, we developed a dual passive driver system for MRE.At 1.5 T MR system (Signa HDxt, GE Healthcare, Waukesha, WI, USA), we performed a phantom study using gradient-echo (GRE) sequence specialized to MRE, and an eight channel phased array receiver. The phantom components were made from agar having different stiffness (0.75 and 1.0 wt%). The electromechanical actuator system had three components; an active driver used as the source of mechanical waves i.e., acoustic, a flexible air-filled plastic tube for through waves, and one or two passive driver that transmitted pressure waves. The passive drivers were set on the right side, left side, and anterior to the phantom. There was a synchronized pulse sequence with 60 Hz mechanical vibrations and 70 amplitudes. A connector for the dual passive driver system was made in-house made (Fig. 1). The GRE imaging parameters were echo time, 19.4 ms; reputation time, 50 ms; field of view, 42 cm; matrix size, 64 × 64; band width, ± 32.3 kHz; slice thickness, 8 mm; and slice, three. The shear stiffness and amplitude wave images were calculated from the acquisition acquired imaging data. Each passive driver setting position and single or dual passive driver were compared the shear stiffness value and the standard deviation on unwrapped phase image (S.D._unwrap), i.e., we regard it as phase shift. of The region-of-interest (ROI) was set on right liver at one slice. Then, unwrapped phase images were calculated as follows [3]; $$ϕ(r)=ϕ_{ w }(r)+2πn(r),$$ where $$$ϕ(r)$$$ is the true phase (unwrapped), $$$ϕ_{ w }(r)$$$ is the wrapped phase, and n(r) is the integer multiple of 2𝜋 needed to produce the true phase for position r. Moreover, we carried out a study using these conditions on a healthy volunteer. The healthy volunteer was a 22 years old man with informed consent obtained.Figure 2 shows the shear stiffness, the amplitude wave, and unwrapped phase images of the phantom and the volunteer in each of the passive driver positions. Table 1 shows the mean shear stiffness value derived from the image and S.D._unwrap value of unwrapped phase image in each phantom section and volunteer images, and mean actual measurement value derived using a penetrometer in each phantom section. The S.D._unwrap values of the dual system were shown to be higher than the value of the single system. Moreover, the shear stiffness values of the high S.D._unwrap driver position systems showed the highest correlation to the actual measurement value (P < .05).MRE using a dual passive driver system may render it possible to obtain more detailed information than that provided by a single passive driver system in the evaluation of liver conditions.