Insulin micropump with embedded pressure sensors for failure detection and delivery of accurate monitoring

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Abstract

Improved glycemic control with insulin pump therapy in patients with type 1 diabetes mellitus has shown gradual reductions in nephropathy and retinopathy. More recently, the emerging concept of the artificial pancreas, comprising an insulin pump coupled to a continuous glucose meter and a control algorithm, would become the next major breakthrough in diabetes care. The patient safety and the efficiency of the therapy are directly derived from the delivery accuracy of rapid-acting insulin. For this purpose, a specific precision-oriented design of micropump has been built. The device, made of a stack of three silicon wafers, comprises two check valves and a pumping membrane that is actuated against stop limiters by a piezo actuator. Two membranes comprising piezoresistive strain gauges have been implemented to measure the pressure in the pumping chamber and at the outlet of the pump. Their high sensitivity makes possible the monitoring of the pumping accuracy with a tolerance of ±5% for each individual stroke of 200 nL. The capability of these sensors to monitor priming, reservoir overpressure, reservoir emptying, outlet occlusion and valve leakage has also been studied.

Figures

  • Figure 1. Schematic cross-section of the micropump (not to scale). The arrow indicates the flow direction. The small rectangles are schematic representations of the anti-bonding structures. The green layer is the buried oxide.
  • Figure 2. Photos of the device (courtesy of Debiotech SA, Switzerland). (a) Pumpcell comprising the micropump mounted onto a ceramic substrate having interconnection pads. (b) Disposable unit with the Pumpcell and the battery (top) mounted onto the insulin reservoir (bottom). (c) Pumping unit ready to be attached onto the patch. The pump controller (top) is assembled with the disposable unit (bottom). (d) Pumping unit and its remote controller.
  • Figure 3. Inner and outer sensor signals during priming.
  • Figure 4. Evolution of the inner sensor signal before and during the five strokes following an occlusion.
  • Figure 5. Evolution of the outer sensor signal before and during the five strokes following an occlusion.
  • Figure 6. Stroke volume as a function of the inlet pressure, in standard and reverse actuation modes.
  • Figure 7. Inner sensor signal versus inlet pressure during an actuation cycle.
  • Figure 8. Stroke volume as a function of the flow rate in standard and reverse modes (for insulin U 100; 1 U/h is equivalent to 0.01 mL/h).

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CITATION STYLE

APA

Dumont-Fillon, D., Tahriou, H., Conan, C., & Chappel, E. (2014). Insulin micropump with embedded pressure sensors for failure detection and delivery of accurate monitoring. Micromachines, 5(4), 1161–1172. https://doi.org/10.3390/mi5041161

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