In this work, we successfully developed highly sensitive non-invasive salivary glucose and pH sensors utilizing interdigitated microelectrodes through a distinctive in-situ pH control method. The electrochemical pH control is an effective approach to produce molecular oxygen, thereby enhancing the sensitivity of the glucose sensor. The feasibility of this technique was demonstrated through COMSOL simulations and subsequent electrochemical characterization using gold IDE arrays in buffered samples. By designing the sensing electrode in close proximity to the protonator electrode, we could tailor the local pH at the sensing electrode to pH 5.5, ensuring precise glucose detection in saliva. SEM, EDX, AFM and EIS data confirmed a change in the surface morphology following each electrode modification step. The successful electro-polymerization of the o-PD/β-CD/GOx layer facilitated enzyme immobilization on the IDEs' surface, enabling low-level glucose detection in both buffer and saliva-based solutions. Both the pH and glucose sensors exhibited linear relationships within a pH range of pH 5 -8 (R 2 = 0.997) with a sensitivity of -71.4 mV.pH -1 , and a range of glucose concentrations from 0.05 -2 mM (R 2 = 0.980) with a sensitivity of -0.76 nA.mM⁻¹, respectively, in buffer-based solutions. Additionally, the pH sensor can detect pH levels in artificial saliva within a range of 5 -9 with a sensitivity of -166 mV.pH -1 . Furthermore, the GOx modified electrodes can detect glucose in artificial saliva at a wide range of concentrations from 0.02 mM to 7 mM, with a LOD of 0.3 µM and an immense sensitivity of -0.46 nA.mM -1 . Moreover, the excellent specificity is attributed to the GOx electrodes modified with β-CD, which enables selective detection against key interfering species such as AA, UA, D-Furc, and Ace. The glucose sensor demonstrated robust performance with fast response (<20 s) and good operational stability over two months of storage. Additionally, the sensors were also able to accurately detect glucose and pH levels in real saliva (healthy and sick calves). However, it is noteworthy that the sensitivity of the sensors appeared to diminish after ~70 days, possibly due to enzyme denaturation or degradation of the immobilization matrix and electrode surface. In conclusion, the device we developed is highly promising in electrochemical sensing systems due to its superior sensitivity, selectivity, and stability. Given the current trend towards biosensing devices with multiplexing capabilities, this study also presents an elegant approach of integrate 4 by using on-chip Pt reference electrode, the oxide reduction peak is seen at approximately 0.05 V (black). pH controlled by biasing the protonator electrodes array at 1.13 V, the oxide reduction peak shifts to 0.075 V (blue) which is the same match as the buffer pH 5.5 (red). (d) Similar approach were applied to control the buffer pH form pH 6.8 to pH 5.5 by applying 1.06 V at the protonator electrodes since the pH of the artificial saliva is pH 6.8. buffer at an initial pH is 7.5, the gold oxide reduction peak is seen at approximately 0.5 V (red). pH controlled by bias ing the protonator electrode array, the oxide reduction peak shifts to 0.63 V (orange). The dashed line shows the location of the gold oxide reduction peak maximum when 1.66 V was applied to the protonator occurring at the same position (violet) as when the solution was acidified to pH 5.5 with acid. .