INTRODUCTION
PMUTs represent a compelling solution for compact, low-power, and portable ultrasound systems, demonstrating suitability for diverse imaging applications [1]. Compared to conventional block ultrasonic transducers, PMUTs offer advantages such as scalability in production, cost-effectiveness, compactness, and compatibility with Complementary Metal Oxide Semiconductor (CMOS) technology. Their favorable acoustic impedance matching with human tissue further underscores their utility [2]. Compared to CMUT ultrasound imaging, PMUT arrays offer advantages by eliminating the need for applying DC bias voltages. Furthermore, PMUT fabrication is less complex due to the absence of stringent requirements for precise gaps of very small depth [3]. However, to achieve optimal performance, PMUTs demand higher pulse-echo sensitivity (equivalent to emission sensitivity × receiving sensitivity) and bandwidth (BW) for enhanced imaging depth, signal-to-noise ratio, and longitudinal resolution. Additionally, ensuring that the pitch of elements within the PMUT array meets the half wavelength rule is critical (for example, underwater frequency>7.5MHz, pitch<100µm) [4].