## 1 Introduction  
In vivo pressure monitoring is a crucial means of assessing organ health. Particularly, high-precision dynamic monitoring of in-body pressure is of significant importance for controlling and treating patients' conditions. For example, early symptoms of atrial fibrillation in patients primarily manifest as arrhythmias, with patients experiencing brief episodes of rapid, slow, or irregular heartbeats. Blood pressure monitoring is needed to assess the heart's condition, thereby obtaining the correct treatment [1; 2; 3]. Similarly, patients with uremia may experience early urine reflux, leading to sustained or sudden increases in renal pressure, gradually exceeding the kidney's tolerance [4; 5; 6]. Early in vivo pressure monitoring within the kidneys can control the damage to the kidneys caused by the disease [7]. Additionally, most patients with cranial diseases require long-term monitoring of intracranial pressure (ICP). When the intracranial pressure is too high, patients may experience a range of clinical symptoms, such as dizziness, nausea, and vomiting. Early and long-term monitoring of ICP in patients can also help in the prevention and treatment of hypoxemia, subarachnoid hemorrhage, tumor-related swelling, and other intracranial space-occupying diseases [8; 9; 10]. Currently, there are many types of in vivo pressure monitoring devices used in conventional medical testing and treatment processes [11; 12; 13; 14; 15], mainly divided into non-invasive and invasive pressure measurement devices, with invasive measurement regarded as the gold standard for pressure monitoring. Non-invasive pressure measurement devices usually employ sensors, such as fiber optic sensors and pressure sensors, to measure in vivo pressure through the human skin, fat tissue, muscle tissue, and external walls of blood vessels [16; 17; 18]. These require specific wearing methods, measurement techniques, and algorithms to achieve in vivo pressure measurements [19; 20; 21]. Although such methods do not harm the patient, their measurement accuracy is lower than that of invasive monitoring devices [22; 23]. At present, in critical settings, such as intensive care units (ICU) and surgeries, clinically more accurate invasive in vivo pressure measurement devices, such as invasive blood pressure (IBP) monitors, are used. An IBP monitor typically employs a puncturing method to place a needle inside the brachial, radial, or dorsal pedal artery. The in vivo pressure is transmitted through a catheter that is 100 cm to 150 cm long, with an inner diameter of less than 2 mm and filled with saline, to the pressure sensor at the end of the catheter. This sensor then measures and sends the pressure signal to the monitor. This method of long catheter pressure transmission can relatively accurately measure the pressure of static or uniformly flowing fluids. However, dynamic changes in the body's fluid pressure cause the fluid to flow within the catheter, resulting in pressure loss, which is related to the overall length and size of the pressure transmission catheter [24; 25]. Longer pressure transmission catheters produce fluid dynamically varying pressure loss, leading to a decrease in the accuracy of dynamic measurement results, making it difficult to meet the increasingly high accuracy requirements of modern measurements. Implantable pressure measurement devices, such as pressure guidewires, are types that directly implant pressure sensors at the measurement points, eliminating the need for a pressure transmission process, hence they achieve high static and dynamic accuracy. However, these devices also have certain limitations: 1. These devices require complex implantation methods (such as surgery) that carry certain risks; 2. Long-term implantation of devices in areas like the cranial or vascular regions can lead to clinical symptoms, such as inflammation and embolism; 3. Such implantable pressure measurement devices embed sensors inside the human body, making it difficult to timely clean or replace the sensors; and 4.