METHOD AND DEVICE FOR SENSING

Abstract: The invention relates to a method for compensation of the potential drift of a reference electrode (RE) in electrochemical measurements of concentrations of at least one dissolved chemical entity in a liquid medium by means of a counter electrode (CE) and a working electrode (WE) and a reference electrode (RE), said method comprising applying at least one measurement potential (E) on the working electrode (WE) relative to said reference electrode corresponding to a measurement voltage U, during at least a part of a measurement period, at which said dissolved chemical entity is subjected to an electrochemical reaction at said working electrode (WE), said reaction resulting in a measurement evoked current, said method comprising the steps of: registering the measurement evoked current IpO2, comparison of the measurement evoked current IpO2 with a predetermined value Iset, decreasing or increasing the voltage U with a value dU in negative or positive incremental steps such that the measurement current IpO2 approaches Iset. The invention also relates to an apparatus for performing such measurements and an active implant having device and the method implemented therein.

Description: Method and device for sensing The invention relates to a method for compensation of the potential drift of a reference electrode in electrochemical measurements of concentrations of at least one dissolved chemical entity in a liquid medium and also to an improved method for measuring the oxygen concentration in a liquid medium and an apparatus to be used with this method using a reference electrode, a working electrode and a counter electrode. The invention also relates to a pacemaker comprising an apparatus according to the invention and the use of a method according to the invention in a pacemaker or the like. In the description the following expressions are intended to have the following meaning: Measuring potential: the applied potential, as related to a reference potential, during the measurement, in the description denoted E, corresponding to a Measuring voltage: used in algorithms denoted U, which are part of the present in- vention. Floating potential: the potential, as related to a reference potential, an electrode will acquire when placed in an electrolyte and no current is allowed to pass through an outer circuit, i.e. not passing through the electrolyte, in the description denoted E 0 . It should be understood that these potentials actually refer to an arbitrarily chosen level, e.g. common ground. Chemical entity: a chemical entity is defined for the purpose of this application as either a gas or a chemical substance or compound dissolved in a liquid medium. Such entities can be subjected to .analysis by electrolytic reduction/oxidation reactions and the corresponding reduction/oxidation potential, or rather the electric current evoked by said potentials for characterizing the amount and substance re- duced/oxidized. Working electrode: herein and below relates to the electrode at the surface of which the reduction of the chemical entity takes place. Sensor Rate: A calculated rate increase to be added to a basic pacing rate when the sensor is used in an active implant. The sensor herein and below being an oxygen sensor comprising a working electrode and a counter electrode and a reference electrode. In modern medicine, implantable heart pacemakers are used increasingly for the therapy of heart arrhythmia. It is a well-known fact that physical demands on the body requires levels of oxygen adapted to the degree of physical activity to be delivered to the body. Thus the body activity lowers the venous oxygen concentration in the blood as a function of the degree of activity. The oxygen concentration in the blood and the changes in the concentration may be used as indicators for a change in the stimulation pulse rate in order to regulate the rate of the stimulation pulses emitted by the pacemaker. It is to be noted that oxygen in the blood exists in an equilibrium. The greater part of the oxygen is attached to the hemoglobin molecules while some part is dissolved in the blood plasma and transported thus through the vascular system including the heart. The amount of oxygen combining with the hemoglobin is dependent on the oxygen's partial pressure in the blood, measurements of either one will give indication as to the amount of oxygen present. There are also other factors, which govern the ability of hemoglobin to combine with the oxygen, such as temperature and pH. The oxygen saturation of the blood, which is a measure of the amount of oxygen bound by the hemoglobin, may be measured by different methods, e.g. transmission photometry and reflection photometry in the venous blood or measured indirectly by electrochemical methods, see above. The photometric measurements do not show a linear dependency on the oxygen saturation and the measurement values have to be compensated in various ways, which is not the case in the electrochemical methods for measuring the oxygen partial pressure. In these later methods there is a linear dependency in the measurements of the measured current as a function of the oxygen partial pressure. The measurements using electro-chemical methods make use of the fact that the oxygen molecules dissolved in the blood are chemically reduced on the surface of the working electrode when the potential during a measurement pulse is forced to negative potential (about 1 volt) relative to a reference electrode/potential. The counter electrode CE is here below assumed, at least partly, to have a surface made from carbon. In the reduction process, hydroxide ions are produced and the amount of these ions are dependent on the concentration of dissolved oxygen according to the reactions: at the working electrode 2 H 2 O + O 2 + 4 e " = 4 OH " at the counter electrode 4 OH " + C = CO 2 + 2 H 2 O + 4 e " The above equations show a simplified picture of the process in the liquid (electrolyte), but for the purpose of this description they are sufficient . The electrical current flowing through the liquid medium to the working electrode WE during the measurement pulses is carried by the hydroxide ions. This current, called the oxygen current (Ipo 2 ), is proportional to the amount of hydroxide ions formed on the WE surface. During the measurement pulse the carbon coating of the counter electrode CE is oxidized to minute amounts of carbon dioxide (CO 2 ), which is removed by the blood stream Patent documents disclosing different aspects of electro-chemical measurement teachings are e g US, 4 602 637, US, 4 61 1 604, US, 4779 618 and US, 4 853 091 A factor influencing these measurements is the dπft of the reference electrode RE One of the more stable reference electrodes that may be used is the Ag/AgCL- electrode However, the bio-compatibility of the reference electrode is important as the reference electrode is to be implanted Other types of reference electrodes with better bio-compatibihty are not as stable as the Ag/AgCl-electrode The Ag/AgCl- electrode also must be protected by e g a membrane when used in vivo because of the above reason It is thus a purpose of the present invention to improve the stability and sensitivity of the appaiatus and the method b\ diminishing the effects of the dπft of the reference electiode Another object of the invention is to increase the overall sensitivity of the measurements Another object is to minimize the vaπations in the amplitude of the measuπng current so as to maximize the sensitivity and to diminish possible side effects from currents πsing above a certain limit Yet another object is reduce as much as possible the amount of energy used for the n easunng pulses and still make certain that a relevant value is attained In accordance with the invention these objects are accomplished by the invention as claimed in the independent claims It has thus surpπsingly been found that the solution to the above stated problems according to the present invention is to perform the measurements using a method, which avoids the problem of the dπft of the reference electrode Dunng testing of electrodes the inventor has observed that the measured oxygen current (the current aπsmg as a result of the voltage imposed between the working electiode and the counter electrode) increases or decreases by time It can, however, be shown that there is an optimal measurement potential where the relative sensitiv- lty is the highest and which decreases on both sides of that optimum When the current decreases the sensitivity also decreases because the measurement potential comes closer to the limit beyond which the reduction no longer takes place On the other hand if the current increases by time the measurement pulse amplitude will have to be reduced since otherwise the πsk for tissue stimulation is obvious Thus, by continuously adjusting the measurement pulse amplitude compared to the so called reference electrode such that the measurement current I p02 approaches the value I set Expeπence from pre-chnical tests has shown that for e g a 7 mm" gold working electrode the measured oxygen current I p o 2 should be about 30-80 μA, depending on the area etc of the working electrode WE, which will give the optimal results for this mateπal Preferred embodiments are represented by the dependent claims The method and the apparatus will prove to be beneficial in several ways By keeping the current close to a set value, e g in the case of the oxygen-blood system 50 μA. it will be possible to obtain the best sensitivity in the measurements, I e the highest vaπation in the measured current as a function of the physical activity as related to rest The invention will be described with references to the following figures: Fig. 1 a and b show a single, respectively a double step measuring pulse that may be used in the measurements. Fig. 2 shows curves relating to the current density through the medium and the oxygen sensitivity as a function of the measurement pulse potential Fig. 3 shows the components of a test system for illustrating the measurements according to the method of the invention. Fig. 4 shows flow sheets explaining the method according to the invention. Fig. 5 shows a circuit diagram of a device according to the present invention. Fig. 6 is a diagram showing the switching of the device in Fig. 5 and the corresponding output voltages. The two diagrams in fig. l a and lb will be further discussed below To simulate the measurements according to the method of the invention and the use of an apparatus according to the invention and to show the relation between the cur- rent densities and sensitivity in measurements, a cell has been set up comprising a working electrode and a counter electrode placed in a physiological saline solution. Through the cell is bubbled a mixture of 6 % O2, 6 % CO2 and 88 % N2 to simulate the amount of oxygen solved in the blood at rest and 2 % O2, 6 % CO2 and 92 % N2 to simulated the amount during hard physical activity. The set up is shown in Fig. 3. The main components are a computer, or the like, with a two-way communication with a potential step potentiostat, which in turn co-acts with an electrochemical cell comprising a fluid medium and immersed into the cell a working electrode (smooth pyrolytic carbon, having an area of 9 mm 2 ), a reference electrode (e.g. an Ag/AgCl-electrode) and a counter electrode. The measurements are controlled by a computer. It should be noted that the system is free-floating between the measurements The vaπation in the sensitivity of the measurements and the current density in A/m 2 vs the impressed potential on the working electrode as related to the reference elec- trode, the reference electrode RE in this case being a Ag/AgCl electrode, is shown in the form of diagrams in Fig 2 The reason for chosing the current density as the vaπable in the above diagram is that the values shown, then will be independent of the area of the reference electrode and different electrodes may thus be compared to each other In the diagram in Fig 2 is given the respective curves for the current density vs U both at rest and activity for a measurement senes taken using a single step pulse and for a senes of measurement using a double step pulse where in the later compensation for the double layer capacitance has been applied In the figure is also shown the calculated sensitivity curves for measurements using a double step pulse with compensation denoted - - 0 - - and for measurements using a single step pulse - - - - The sensitivity curve indicates the difference between the current density at work and at rest in % of the current density at rest From the step voltammogram curves is noted that the sensitivity curve for the double step pulse with compensation shows a higher sensitivity than that from the use of single step pulse without compensation Also may be noted by companson of the curves representing rest and the curve representing activity that, when the respective measurement curves for the two methods, single step without compensation and double step with compensation, respectively, for U having small values are compared, the curves at first follow each other closely and with an increasing U the gap between the two curves widens to a maximum and thereafter the gap shows a tendency to essenti.ally remain constant as the current density increases The above measurements illustrate the sensitivity peak and the influence thereon from two different types of measurement pulses The method according to the invention is herebelow descπbed with reference to two different flow-sheets descπbing two embodiments of the method It should be appreciated that the two embodiments may be each be combined with the two types of measurement pulses descπbed in connection with Fig la and b below The first method descπbed in the flow-sheet in Fig 4a makes use of a set of initial values as follows In block A of Fig 4a the ιnιtι.al values are set The measurement voltage U is chosen to correspond a current I set = 50μA, e g 800mV, a time between measurements T = 1 5 sec , an incremental step to be applied to the measuπng potential dU = ImV and a set number of cycles to be run through N= 100 before the measurement cycle is restarted The value of dU in the two instances where it is used in the algoπthm could ol course be set as two separate values dUi and dU 2 In block B a counter "I" is set to "1 " Decision box C represents a waiting loop used for synchronizing the measurements to some event in the heart, e g an atπal or a ventricular stimulation pulse, a P-wave or a QRS-complex, for the measurements The loop through decision box C is run through until "R/P^" is set to "TRUE", l e the specified event has occurred At this point the I p02 , ι e the oxygen dependent current ansing from the reaction of the oxygen at the working electrode WE, is determined by applying the measurement potential E (block D) In block E a value I sβns is calculated as I sen s = In decision box F it is checked if this value I se „ s > 0 If this is the case the applied measurement voltage is decreased immediately with a value dU in block G and I sβlls is set to "0" in block H In block J a rate increase SR (Sensor Rate) dependent on the measured pO 2 is set according to the formula SR = -K*I sens K may be a vaπable, programmable or a set value In decision box K a test is made "Timer =T^" If it is not the decision box is run through unul the value of "Timer =T^" is "TRUE" and then in block L the timer is reset to "0" In decision box M it is then tested if "I < N" If it is "TRUE" the value of "I" is increased by "1" in block O and return is made to decision box C Returning to decision box M, if the value of "I < N" is "FALSE" an increase of the measurement potential U is made with an increment of dU Thereafter the procedure starts again in block B where "1" is set to "1 " The reason for the loop C - M, O. C to be run through a set number of times N before an increase is made in the measuπng voltage U is to attain a slow adaptation of the I p o 2 to I set If the adaptation was to take place immediately there would hardly be any difference in the value I sens determined from cycle to cycle and thus no possibility to determine an increase in SR in block J The above implies that, if the oxygen content of the blood decreases due to e g exercise, the oxygen dependent current I p02 decreases, and I Sθns increases, and the rate is set accordingly If, on the other hand, the oxygen dependent current is increasing above I sβt due to e g drift of the reference electrode, a fast adaptation of the measuring potential U is effected After N cycles an increased measurement potential is used which in turn will be fast adjusted downwardly if indicated by the next measurement In a second method a mean value for I p02 being the measured current at each measurement, is calculated at the end of the N number of cycles This is not done m the method according to Fig 4a The second method descπbed in the flow-sheet in Fig 4b likewise makes use of a set of initial values as follows In block A of Fig 4b the initial values are set The measurement pulse is adjusted to give a current I set = 50μA, a time between measurements T = 1 5 sec , an incremental step to be applied to the measuπng potential dU = ImV and a set number of cycles to be run through N= 100 before the measurement cycle is restarted The value of dU, which is used in three instances in the algoπthm could of course be set as three different values, on for each instance, dUi, dU 2 , and dU 3 In block B a counter "I" is set to "1 " Decision box C represents a waiting loop used for synchronizing the measurements to some event in the heart, e g an atπal or a ventπcular stimulation pulse, a P-wave or a QRS-complex, for the measurements The loop through decision box C is run through until "R/P?" is set to "TRUE", I e the specified event has occurred At this point the measurement of the I p o 2 (0 > l e the oxygen dependent current aπsing from the reaction of the oxygen at the working electrode WE, is performed by applying the measurement potential U in block D In block E a value I sens is calculated as I se ns = l P o2( - Iset In decision box F it is checked if this value I sβns > 0. If this is "TRUE" the applied measurement potential is decreased immediately with a value dU in block G and I sβns is set to "0" in block H. In block J a rate increase SR, dependent on the measured I p o 2 , is set according to the formula SR = -K*I sens . K may be a variable, programmable or a set value. In decision box K a test is made "Timer =T?". If it is not the decision box is run through until the value of "Timer =T?" is "TRUE" and in block L the timer is reset to "0". In decision box M it is then tested if "i < N". If this is "TRUE" the value of "i" is increased by "1 " in block O and return is made to decision box C. If the value of decision box M is "FALSE", a value I mean is calculated in block N according to the formula I mβan = Σ I p o 2 (i) N. In decision box P the value I mean < I set is checked. If it is "TRUE" U is increased in block Q with dU and if it is "FALSE" the value of U is decreased in block R with a value of dU. After either of block R and block Q return is made to block B in which "i" is set to "1 ", and the measurement cycle is stared over again. In the above algorithm consequently a check is made after a time T = the set value, e.g. 1.5 sec, as to the number of cycles N. If the number of cycles run through equals N a calculation of a value I mβan = Σ I p o 2 (i) / N is performed. A comparison thereafter made I mβa „ < I Sθ t I "TRUE" the measurement potential is increased with an amount dU and if "FALSE", a decrease of the measurement potential with an amount dU is made. The above implies that, if the oxygen content of the blood is decreasing, the rate is increased accordingly. After N cycles the measurement potential is adjusted towards the value that gives a I mβan = I set . In a further embodiment of the methods described there is provided a possibility to vary the amount dU with which U is increased or decreased by making the value of dU a function of I sens in the measurements according to the methods described in connection with Fig. 4a and Fig. 4b. In a preferred embodiment of the method according to the invention the methods are used in an active implant such as a pacemaker or the like. The implant should preferably be of the type which senses the heart activity and also paces the atrium and/or the ventricle. The rate adjustment provided for in the method according the invention is the used to control the implant, such that the pacing is adjusted continuously. These methods are above can be performed in the form of a single measurement of the current during the measurement pulse. However, in order to compensate for especially the double layer capacitance of the electrode the preferred procedure is to integrate at least a part of the current caused by the measuring pulse over time and actually use this value for the control of the applied measurement potential. This will be described further in connection with the switching diagrams in Fig. 6. A preferred device for accomplishing these measurements according to the algorithms in Fig. 4a and 4b, is shown in Fig.5. The circuit diagram in Fig. 5 comprises three main parts. Part 10 comprises the circuitry connected with the counter electrode CE and the reference electrode RE. Part 20 comprises the liquid medium (the electrolyte) in which the counter electrode CE, and the reference electrode RE are immersed together with the working electrode WE. Part 30 comprises the circuitry connected to the working electrode WE. This part also comprises a current amplifier and an integrating circuit. A part 40 denotes a control unit for performing the steps of the method according the invention. The control unit 40 compnses among other things a microprocessor, a ROM in which a program implementing the invention for example in the form of the processes shown as examples in connection with Fig 5 and Fig 5a may be stored, a RAM for stoπng and calculating data from the measurements and the calculations performed, input means, such as a programmable unit to be used in conjunction with a programmer (the programmer is a separate device used for commumcation with the active implant) in order to set initial values for the algoπthm to be executed by the program, input channels for providing measurement data to the microprocessor, and A/D-converters for conversion of analog values measured in the process to serve as input data to the stored program, output channels from the microcomputer for sending control signals to control the measurements and to the vaπous switches to be opened and closed dunng the different modes of the measurements When the device is implemented in a pacemaker as a part thereof, the programmable umt may be integrated in the control umt for controlling the pacing parameters Also data channels for transfer of data such as P-wave etc indications etc may be provided in order to use these in e g the rate algoπthm descπbed Part 10 has a voltage source VS, the positive terminal of which is connected to a switch SI The negative terminal of the voltage source VS is connected to a common ground A capacitor Cl and a switch S2 are coupled together in senes and are in parallel with the voltage source VS and the switch SI The capacitor Cl is connected on one side to the common ground The non-inverting input of an operational amplifier El is connected to a point between the switches SI and S2 The inverting input of the same amplifier El is coupled to the non-inverting input of an operational amplifier, coupled as a voltage follower E2 The output of the operational amplifier El is coupled via a switch S4 to the counter electrode CE The reference electrode RE is coupled to a point between the inverting input of the said amplifier El and the non-inverting input of the amplifier E2 The output of the operational amplifier E2 is thus coupled to the inverting input of E2 (voltage folio wer)and via switch S3, to a point between switch S2 and capacitor Cl Part 20 compnses the electrodes and the medium in which the measurements are to take place The working electrode WE is connected to the inverting input of a operational amplifier E3 in circuit part 30 The non-inverting input of the same is connected to the common ground Parallel to the output of E3 and the inverting input of the same a resistor Rl (10 kΩ) is arranged A switch S5 is connected in senes to the resistor R2 (100 kΩ), which is coupled to the inverting input of E4 In the negative feedback loop of E4 the capacitor C2 and the switch S6 are connected in parallel The sample and hold circuit compnses this last mentioned operational amplifier E4 having the inverting input connected to R2, the non-inverting input to the common ground Said circuit also compnses the switch S6 and the capacitor C2 The two diagrams in fig la and lb each show the relationship of a controlled and a floating potential of the working electrode WE as related to the reference electrode RE vs time The dashed line signifies a free-floating state E 0 of the electrode when no current is flowing to the working electrode WE while the continuous lines represent the controlled potential E applied to WE dunng measurements The type of pulse shown in Fig la represents a single step pulse and in Fig lb a double step pulse for eliminating the influence of the double layer capacitance The switching diagram in Fig 6 shows two vanants (type 1 .and type 2) of the switching modes for a measurement cycle of the device, and the resulting voltage on the output from the operational amplifiers in points A, B and C designated u(A), u(B), and u(C), respectively. The two switching diagrams correspond to the single step (type 1 ) and double step (type 2) measuring pulse shown in Fig. la and Fig. lb. The switching diagrams and the curves of the potentials in point A, B, and C are drawn to the same time-scale. It can thus be seen that in the single step (type 1) the measurements will be performed between t = t 3 and t , and in the double step (type 2) the measurements will be performed between t = t 3 and t , .and between ts and t_, and these measurements will be added on C2 in order to diminish the effects of the double layer. The voltage source VS in figure 5 generates the desired measurement potential U. The value of U can be varied by a digital-analog-converter (DAC) controlled by a control unit. Just before the measurement pulse the integrating capacitor C2 is short- circuited by switch S6, C2 thus being reset. To generate a type 1 single step pulse the switches SI , S2 and S3 are not changed (SI is closed and S2, S3 are open all the time). When S4 is closed El will control its output so that its inputs are equal. Then the potential of the reference electrode will be the same as the voltage U. When S4 is open no current will flow through the electrochemical cell. The potential of the working electrode WE in this system will always have a potential equal to the common ground. This is a result of the current amplifier E3, which also gives an output voltage proportional to the measurement current due to u(B)=Rl *I. ( Note that in Fig.1 the potential of the working electrode WE is shown in relation to the reference electrode RE) To generate a type 2 double step pulse the potential of the reference electrode just before the pulse is stored on capacitor Cl . When the voltage follower E2, which charges Cl to the floating reference potential, is disconnected by switch S3, the voltage over Cl remains at that potential. At the first step the positive input of El is connected to the voltage source VS, at the second step it is connected to the capacitor Cl These two voltages are then sequentially imposed on the reference electrode In the diagrams denoted u(A), u(B) and u(C) in Fig 6 the voltage at each instant is shown at the corresponding points (shown in Fig 5) The voltage shown in point C is proportional to the oxygen current through the cell and may therefore be integrated over time to give the results in the form of an amount of electnc charge After the measurement pulse the integrated current is held on the output of E4 to the next pulse Rl «{C) = U{p02) - ——\ l *dt C2 * R2 This voltage U(p 02 ) is fed back to the control umt, in which I p o2 is calculated from u(C) and compared to the set current I set It may be provided for in the algoπthm used for controlling the measurements a possibility of stopping the sensor rate from πsing to high, however this may also be provided by setting a maximum sensor rate in the pacemaker itself The invention has been descnbed in connection with the process of sensing of oxygen in blood measurements, however there is a general pnnciple involved in the method and device, which concerns the use of only three electrodes in this type of measurements and in which through the method of measurement and the descπbed apparatus the influence of the dπft in potential of the reference electrode is substan- tially dimimshed This means that the invention as descnbed generally applies to this type of measurements regardless of the substances involved The rate adjustments which in the descnbed application in used for adjusting the pacing rate of an active heart implant, a pacemaker or the like, could just as well in other applications be used to regulate the addition of a substance or to adjust some parameter such as tem- perature in a temperature dependent reaction The method may be generally adapted to other media than blood as the liquid medium and to oxygen as the measured entity. The entity may also be represented by other gases in liquids and by chemicals dissolved in liquids. The apparatus as well may of course likewise be used for other media.

Claims: Claims 1 A method for compensation of the potential dπft of a reference electrode (RE) in electrochemical measurements of concentrations of at least one dissolved chemical entity in a liquid medium by means of a counter electrode (CE) and a working electrode (WE) and a reference electrode (RE), said method compπsing applying at least one measurement potential (E) on the working electrode (WE) relative to said reference electrode, corresponding to a measurement voltage U, dunng at least a part of a measurement penod, at which said dissolved chemical entity is sub- jected to an electrochemical reaction at said working electrode (WE), said reaction resulting in a measurement evoked current, said method compπsing the steps of registeπng the measurement evoked current I p02 , compaπson of the measurement evoked current I p02 with a predetermined value I sθt , decreasing or increasing the voltage U with a value dU in negative or positive incremental steps such that the meas- urement current I p02 approaches I sβt 2 A method according to claim 1 characterized in that said voltage U is adjusted in increments in dependence of a value I S ens = I P 02 - Iset, such that when I sen s > 0, said voltage U is decreased with dU and said voltage U is increased with dU after a predetermined number of cycles N 3 A method according to claim 1 characterized in that said voltage U is adjusted in increments in dependence of a value I sβn s = I P o 2 - Iset, such that when I sβns > 0 said voltage U is decreased with dU and in that after a predetermined number N of cycles a mean value I mβan = ∑I P02 (ι)/N is calculated, and that said voltage U is increased if I m ea n < Is e t and decreased if I mβan ≥ I Sθt with an amount dU 4 A method according to any of the preceding claims characterized in that said liquid medium is body liquids, preferably blood and said chemical entity being oxygen 5 A method according according to any of the preceding claims characteπzed in that before each measurement the working electrode WE is placed in a free- floating state 6. Apparatus for electrochemical determination of concentration of a chemical entity, e.g. oxygen in a liquid e.g. blood or in living tissue having a working electrode WE, a reference electrode RE and a counter electrode CE and means for applying a measurement potential E on the working electrode WE relative the reference electrode RE, corresponding to a measurement voltage U, such that said chemical entity reacts by oxidation or reduction at the working electrode WE , said reaction resulting in a measurement evoked current, and having means for comparison at intervals of the measurement evoked current I p02 to a predetermined value I set , means for adjustment of the measurement voltageU by dU in iterations such that the meas- urement current I P02 approaches I Sθt . 7. Active implant such as a pacemaker, defibrillator or the like adapted for the use of at least a working electrode WE, and a counter electrode CE characterized in said active implant being adapted for measurement of the oxygen concentration variations in the blood by means of the oxygen sensor, comprising a working elec- trode WE, a counter electrode CE and a reference electrode RE, and means for applying a measurement potential E on the working electrode WE relative the reference electrode RE, corresponding to a measurement voltage U, such that said chemical entity reacts by oxidation or reduction at the working electrode WE , said reaction resulting in a measurement evoked current, and having means for comparison at intervals of the measurement evoked current I p o 2 to a predetermined value I se t, means for adjustment of the measurement voltage U by dU in iterations such that the measurement current I P02 approaches I Sθt . 8. Active implant according to claim 6 characterized in having means for synchronizing of the application of the potential E as a function of sensed or paced events of the heart, such as QRS, p-wave, etc. and a control unit for control of the stimulation pulse rate. 9. Active implant according to claim 6 or 7 characterized in said impl.ant having means for rate control of the pacemaker in dependence of the calculated I sens .

Inventors: HOLMSTROEM NILS, HOLMSTROEM, NILS
Applicants: HOLMSTROEM NILS, PACESETTER AB, HOLMSTROEM, NILS
Application year: 1998
Main classification: G01N28
IPC codes: A61N1, G01N27