# Design, Modeling, and Analysis of Piezoelectric-Actuated Device for Blood Sampling
## 1 Introduction and Purpose of the Study  
Blood diagnostics has become a common requirement for investigating the number of diseases, namely, diabetes, HIV, malaria, dengue, thyroid, etc. According to the International Diabetes Federation (IDF), it is now a disease that affects 463 million people worldwide, out of which 187 million do not even know they have the disease. Researchers estimate that the diabetes dilemma will only increase by 2045, with around 700 million people having the disease. There are 180 million patients needing regular diagnostic worldwide, requiring self-diagnostic tools, i.e., a glucometer [1]. The present study was an attempt to design a wearable device to fill the gap. In recent years, various researchers for diagnosis of disease have investigated piezoelectric-actuated devices. The review on piezoelectric micropump carried out by various researchers suggested their effectiveness. The precision driving control and high performance can be used in the biomedical applications [2; 3; 4]. The investigation was carried out on the performance of a val valveless micropump with the help of simulation and experimentation. For the simulation, ANSYS and ANSYS CFX were used for the structural and fluid domains, respectively [5]. The numerical analysis was carried out with consideration of the three-way coupling of a piezoelectrically actuated valveless micropump (PVAM) [6]. A piezoelectric-based micropump with cantilever valve was used for drug delivery application [7]. The authors concluded that shorter cantilever valves gave a higher flow rate. [PERSON] et al. designed the e-Mosquito system for blood glucose measurement [8]. [PERSON] et al. developed a blood extraction system, working at 20 V, for diabetic patients to enable self-monitoring of blood glucose. The experiments were carried out at 20 V,which is a high-energy requirement, as per a wearable device [9]. The simulations on the micropump model, based on finite element analysis, were also carried out [10; 11; 12]. The micropump optimization was done with the diameter of the pump chamber, pump membrane, and needle diameter, but other parameters were not considered by the authors [13; 14]. The numerical study was carried out on the piezoelectric micropump considering various parameters, namely, valve length, angle, applied voltage, and piezoelectric actuator length [15]. The micropump was pumping 0.75 \(\mu\)L/min of water at the back-pressure of about 5 MPa with two active valve-based micropumps actuated by a paraffin actuator [16]. [PERSON] and [PERSON] investigated the effect of actuation voltage and frequency on pump diaphragm deflection and flow rate. They computed time-averaged velocity fields to predict the effect of applied voltage and actuation frequency on the flow rates [17]. With the increase of actuation frequency of the actuator, the flow rate increased up to the first natural frequency [13]. The design of actuator is governed by actuation voltage, ranges of operating frequency, maximum flow rate, and back-pressure. [PERSON] et al. in their paper proposed a new design of strip piezoelectric bimorph disc actuator (SPBD) towards achieving a more practically feasible solution. They conducted detailed numerical analysis to observe effect on flow parameters and concluded that strip piezoelectric bimorphs joined with silicone diaphragm gives improved performance compared to the circular disc actuator [18]. Applied voltage and static pressure had a linear relationship for a certain applied frequency. When a piezoelectric actuator was excited at the resonance frequency, the best result for the static pressure head was obtained [19]. The driving system of the micropump was improved by adding a negative-biased field to the driving voltage. The negative bias increases the displacement of the diaphragm and the flow rates [20]. A critical review was carried out in the probable use of micropump technologies in the biomedical applications.