to the anode 1 to the conducting track 6 running to the cathode 2 preferably the resistor 7 is arranged below the insulating layer 8 in principle however it is also possible to use the resistor 7 to connect the connection sided ends of the conducting tracks 5 6 projecting from under the insulating layer 8 fig3 shows a measurement example of the voltage supplied by the sensor in millivolts along with the hydrogen peroxide concentration in millimoles over the time t in seconds therein the left hand ordinate indicates the voltage u in millivolts for the measurement curve a and the right hand ordinate indicates the hydrogen peroxide concentration in millimoles for the associated concentration graph which is represented by curve b as can be seen a new equilibrium voltage develops between the anode 1 and the cathode 2 across the load resistor 7 within a few seconds when the hydrogen peroxide concentration rises in a step like manner fig4 shows a measurement example of the voltage u supplied by the sensor in millivolts in relation to the glucose concentration in millimoles liter therein it can be seen that the electrical voltage between the anode and the cathode is higher as glucose concentration increases for this reason the associated glucose concentration can be determined with a calibration curve based on the measured voltage an analyte concentration can therefore be determined by measuring the voltage dropping at a resistor 7 which connects a conductor 5 running to the anode to a conductor 6 running to the cathode fig5 shows a further embodiment of a sensor according to the invention fig6 is a longitudinal sectional view of fig5 in essence the sensor shown in fig5 and 6 differs from the embodiment.