Spin echo imaging, due to its robustness to field inhomogeneity and chemical shifts, is one of the most commonly used imaging method in clinic. Despite the popularity, it acquires a single line of k-space per excitation and is slow. To accelerate the data acquisition, several methods such as Fast Spin Echo (FSE)¹, Gradient echo And Spin Echo (GRASE)², parallel imaging³, compressed sensing⁴, and MR fingerprinting⁵ have been proposed. Among them, the GRASE method acquires multiple echoes (typically three echoes) per excitation and, therefore, accelerates the total scan time by the number of echoes. However, due to significant phase difference between echoes acquired in different positions, GRASE images suffer from artifacts. In this study, we propose a new fast acquisition trajectory, Dual Echo Trajectory (DuET), which acquires two partial echoes immediately before and after the spin echo time (Figure 1) to accelerate data acquisition and minimize phase difference between two echoes.The readout of the conventional spin echo sequence was modified to acquire two partial echoes in a single excitation. The two partial echoes were positioned symmetrically around the spin echo time, and a gap time (Δt), the time difference between the spin echo time and the partial echo center (Fig. 1a), was minimized. As a result, both echoes closely resembled spin echo signals, reducing image artifacts. Between the two echoes, a phase encoding gradient was added to acquire different lines of k-space in each echo, thus accelerating the image acquisition by a factor of 2. To minimize potential artifacts from the gap, phase encoding of the two echoes were ordered as shown in Figure 1b; the former echoes filled the central portion of the k-space whereas the latter echoes filled up the rest (Fig. 1 b). The remaining k-space areas (white areas in Fig. 1b) were completed using a modified version of the partial-k-space reconstruction method using a projection onto convex sets (POCS) algorithm.⁶The proposed method and conventional spin echo imaging method were used to acquire the same slice in a healthy subject using a 3T scanner. For both scans, an off-resonance RF pulse was used to saturate fat signal to avoid artifacts in the proposed method. The scan parameters were as follows: single slice, FOV = 256 × 256 mm², resolution = 1 × 1 mm², slice thickness = 5 mm, TR/TE = 600/13 ms, gap time Δt = 0.45 ms, and center strip width = 40 samples. Prior to data acquisition, a few dummy TR was acquired to avoid non steady-state artifacts. Scan time was 2.56 minutes for the conventional spin echo imaging and 1.31 minutes for DuET.Figure 2 shows a reference conventional spin echo image (Fig. 2a), a DuET image (Fig. 2b), and their difference image in percent errors (Fig. 2c). The image difference was on average 2.5 percent in most areas except for the areas of inherent reconstruction error in the partial k-space reconstruction (e.g. vessels). No additional SNR loss occurred compared to single dimension partial k-space acquisition by the same data proportion.In this work, we demonstrated the potentials of using DuET in accelerating the spin echo sequence. The two echoes have spin echo like characteristics and provide high quality images. The method is also compatible with other fast imaging methods such as FSE, GRAPPA and SENSE for further acceleration. The future work includes reduction of reconstruction error by refining phase encoding orders to reduce phase discontinuity.