## 1 Introduction  
Among surgical techniques for treating solid tumors, high intensity focused ultrasound (HIFU) is a promising noninvasive approach to destroy cancerous cells [1; 2]. Unlike conventional radiation therapy, HIFU can kill diseased tissues without causing collateral damage to normal surroundings [3; 4; 5; 6]. The high-power ultrasound waves generated from the HIFU transducer are focused on a specific region to induce thermal necrosis at the abnormal tissue position. The commercial electrical HIFU system is used to drive the HIFU transducer output power for the sake of particular applications.  
With a typical electric HIFU framework, a low power waveform signal created by the commercial waveform generator is transmitted to the RF power amplifier which intensifies the waveform before applying it to the HIFU transducer through an impedance matching network [7; 8; 9; 10]. The operation frequency of the system is modified from 1 to 5 MHz, and it is able to deliver power up to hundreds of watts. Unfortunately, this kind of arrangement is beyond several laboratories' budgets [11]. It requires a lot of financial effort of certain lab-based researchers to conduct a small experiment. Thus, the motivation for this study was to create a compact, feasible system that is more cost-effective than alternative solutions, thus prompting widespread applications of this technology.  
In thermal therapy, overheating leads to unexpected severe denaturation of tissues, leading to organ damage; thus, temperature control is critical for HIFU treatment [12; 13; 14]. The recommended temperature of 60 \({}^{\circ}\)C needs to be maintained at the focal point with sufficient time to coagulate the tumor and be harmless to the tissue [15]. The thermocouple sensor is a possible solution for thermal monitoring due to its primary benefit of rapid response time [16; 17; 18]. Several prior studies have discussed the feasibility of fuzzy logic algorithm to weather uncertain objectives like the temperature [19; 20; 21]. With feedback from the thermocouple, a fuzzy controller is applied to the system to manipulate the target temperature in real-time during HIFU treatment.  
Additionally, for effective monitoring of the experimental study, a reliable imaging-guided method is integrated. For clinical applications, there are two common types of image guidance: ultrasound (US) [9; 10; 22; 23] or magnetic resonance imaging (MRI) [14; 24; 25; 26]. Guided imaging is useful for preliminary diagnosis, treatment planning, and real-time response monitoring. However, a large space required for setup and the costly expense charged for the system are the downsides of these techniques. On the contrary, in the laboratory environment, another option called photoacoustic imaging (PAI) is also used to meet the HIFU monitoring requirements. Factors influencing a successful HIFU cancer therapy are: (i) precise positioning of the tumor region before treatment, (ii) the HIFU beam is focused with sufficient spatial accuracy and selectivity to the region of interest (ROI), (iii) the tissue status is monitored during treatment, and (iv) post-treatment evaluation of the tissue ablation's size. PAI provides the opportunity to handle all four requirements [27; 28; 29; 30]. The vascular increase in the tumor area leads to photoacoustic (PA) image contrast that can be utilized to locate the tumor. Once defined, the HIFU beam is required to accurately deliver acoustic power so that it can locally destroy the tumor without damaging the normal surrounding tissues.  
This study proposes the integration of the fuzzy controller supporting the HIFU system with PAI design. A thermal methodology using the combined structure was constructed to administer treatment for artificial chicken breast tumors. The process has been described in detail, and the subsequent discussion is aimed to overcome remaining limitations to be more feasible for clinical applications in the future.