Radiofrequency (RF) coil engineers, MR scientists with an interest in knee imaging at high fields.Magnetic resonance imaging (MRI) is a very important non-invasive modality for the diagnosis of knee anatomy and pathology. The use of 7 Tesla systems for knee imaging can provide higher signal-to-noise ratios (SNR) than lower field systems. In this work, a novel 8-channel transceive open knee coil for dynamic musculoskeletal (MSK) MR imaging of the knee is simulated and constructed. The open design concept will facilitate the diagnostic and functional assessment of knee injuries and pathology, and allow for imaging of a moving knee. Installing an RF shield around the coil reduces radiation losses and unwanted coupling with the patient bed as well as shielding the other leg of the patient.Figure1 shows the single loop structure. It consists of two multilayered blades in Z direction connected by two horizontal PCB’s with additional tuning/matching capacitors. The size of the gaps on the multilayered structure controls the capacitance of the blade. The tilted angle of the multilayered structure is optimized to achieve the optimum field pattern at the resonance frequency (297 MHz). This design of the blades could improve the RF penetration depth and regulate the mutual coupling between the array elements [1-2]. Figure 2 shows the structure of the prototype transceive coil array. The coil consists of 8 loop-elements (placed in two rows) positioned on a cylindrical section of 180mm in diameter and a length of 200mm in z-direction. The RF shield was placed inside the coil housing 30mm radially away from the array elements. Figure 3 shows the decoupling technique for different individual coils. In order to decouple loops which are in the same raw or column, small inductive decoupling loops are formed in the corner or the edge of each loop to decouple from the adjacent loops. Inductively coupled 8-shape loops are positioned between the coil elements and the RF-shield to decouple the cross loops (for example loop #1 and #6).The coil parameters are optimized using the EM full wave simulator Ansoft HFSS. The tilted angle and the gaps in the blades are optimized for the optimum field pattern and the best decoupling between the loops. Also, the shape and size of the decoupling loops are optimized to achieve decoupling between the loops better than -20dB. The optimization runs with the presence of an RF shield and a homogeneous knee phantom with the following parameters: radius = 85mm, height = 200mm, εr=48.6 and σ=0.6. The optimized array shows decoupling better than -20dB, and port matching to 50Ω better than -20 dB as well. Figure 4 shows the magnetic field distribution in two different symmetrical planes for both the loaded and the unloaded coil. The first is a horizontal plane cut in the centre of the coil (between the two rows), and the second is a symmetrical vertical plane cut (plane A-A in Fig.2). The field pattern shows good homogeneity in the region closer to the inner coil loops (where the knee will be positioned), while it tails off in the open region. The first prototype of the knee coil has been fabricated and assembled as shown in Fig.5. Bench testing for the fabricated coil shows a good agreement with the simulated results.This work presented the design and fabrication of a new 8-channel transceive open knee coil. Both the simulation and the bench experimental results show excellent agreement.