MEDICAL DEVICE PROVIDED WITH SENSORS

Abstract

The invention relates to a medical device (12) comprising an electrical measurement circuit (16), in which are connected at least two variable-impedance sensors (22), the impedance of which varies according to a detected physical quantity, an electrical power source (18) for supplying power to the electrical measurement circuit (16), an antenna (18) for emitting an electromagnetic field according to the impedance of the electrical measurement circuit (16), each of the sensors (22) being associated with a switch (24) for interrupting the current supply of the sensor (22) in said measurement circuit (16), the medical device (12) additionally comprising a system (26) for controlling the switches (24) in order to successively control the opening or the closing of the switches (24), according to determined configurations. The medical device (12) may in particular be applied to the human body or implanted within the human body.

Claims

1.-34. (canceled)

35. A stent, comprising: a plurality of impedance sensors, wherein one or more of the plurality of impedance sensors are positioned on an abluminal surface of the stent; and a communication circuit configured to communicate data regarding impedance from the stent to a computing device; wherein the stent is configured to be implanted in a body of a patient.

36. The stent of claim 35, wherein one or more of the plurality of impedance sensors are positioned on a luminal surface of the stent.

37. The stent of claim 35, wherein: the stent comprises a mesh; and one or more of the plurality of impedance sensors are fixed to a vertex of the mesh.

38. The stent of claim 35, wherein: the stent comprises a mesh; and one or more of the plurality of impedance sensors are fixed to a mid-point of a side of the mesh.

39. The stent of claim 35, wherein: a first group of the plurality of impedance sensors are positioned on the abluminal surface of the stent; a second group of the plurality of impedance sensors are positioned on a luminal surface of the stent; and the impedance sensors of the first group and the impedance sensors of the second group are disposed at opposite positions at common points along a body of the stent.

40. The stent of claim 35, wherein: the stent comprises a mesh, wherein the mesh comprises a plurality of struts; the stent comprises a plurality of measurement lines, wherein each of the plurality of measurement lines comprises two or more of the plurality of impedance sensors; and the plurality of measurement lines are woven between struts of the plurality of struts.

41. The stent of claim 35, wherein: the stent comprises a plurality of measurement lines, wherein each of the plurality of measurement lines comprises two or more of the plurality of impedance sensors; and the plurality of measurement lines extend along the stent in imbricated helices.

42. The stent of claim 35, further comprising: an hyperplasia-limiting coating on one or more of the plurality of impedance sensors.

43. The stent of claim 35, wherein: the stent comprises an electronic measurement circuit, wherein the plurality of impedance sensors are connected to the electronic measurement circuit; and the electronic measurement circuit is implanted in an electrically insulating and biocompatible polymeric substrate.

44. The stent of claim 35, wherein: the plurality of impedance sensors are arranged in series in a measurement line; and each impedance sensor of the plurality of impedance sensors is associated with a respective switch of a plurality of switches, wherein each of the plurality of switches are configured to regulate power to a respective impedance sensor of the plurality of impedance sensors.

45. The stent of claim 35, wherein: the plurality of impedance sensors are arranged in a plurality of measurement lines; a measurement line of the plurality of measurement lines comprises at least two impedance sensors arranged in series; and each impedance sensor of the plurality of impedance sensors is associated with a respective switch of a plurality of switches to regulate power to each of the plurality of impedance sensors.

46. The stent of claim 35, further comprising a plurality of control circuits arranged in series with respect to one another, wherein: the plurality of impedance sensors are arranged in series in a plurality of measurement lines; each impedance sensor of the plurality of impedance sensors is associated with a respective switch of a plurality of switches; and each control circuit of the plurality of control circuits is configured to control one or more associated switches of the plurality of switches to regulate power to a respective impedance sensor of the plurality of impedance sensors.

47. A medical system, comprising: an implantable medical device, comprising: a measurement circuit comprising one or more impedance sensors; and a power source; and a computing device configured to communicate with the implantable medical device and receive data regarding impedance from the implantable medical device.

48. The system of claim 47, wherein the implantable medical device further comprises: an antenna to emit an electromagnetic field according to an impedance of the measurement circuit; and an analogue/digital converter situated between the measurement circuit and the antenna.

49. The system of claim 47, wherein the measurement circuit further comprises: a resistor between two sensors of the one or more impedance sensors, wherein the resistor comprises a fixed impedance.

50. The system of claim 47, wherein the implantable medical device further comprises: a plurality of measurement circuits, each comprising a measurement line comprising one or more sensors, wherein the measurement lines are mounted in parallel; and a plurality of line selectors, wherein each line selector of the plurality of line selectors is associated with a respective measurement line and configured to control current supply to the respective measurement line.

51. The system of claim 47, wherein the computing device further comprises an antenna configured to emit an electromagnetic field to induce power in the measurement circuit.

52. The system of claim 47, wherein the measurement circuit of the implantable medical device comprises at least one circuit to generate an electrical signal at a frequency, the electrical signal to be applied to anatomy contacted by the implantable medical device and to be received by an impedance sensor of the one or more impedance sensors.

53. A method of operating an implantable medical device, comprising: successively controlling opening and closing of a plurality of switches of a measurement circuit, the measurement circuit comprising a plurality of sensors each associated with a respective switch of the plurality of switches, such that each of the respective switches are selectively electrically connected between a power source of the implantable medical device and an antenna of the implantable medical device; and adjusting an electromagnetic field emitted by the antenna of the implanted medical device at a time to be indicative of a value measured at the time by a sensor of the plurality of sensors.

54. The method of claim 53, further comprising at least one of: with a comparator of the implantable medical device, comparing an identifier emitted by a computing device separate from the implantable medical device with a binary code associated with at least one fixed impedance of the implantable medical device; or with a computing device separate from the implantable medical device, analyzing a portion of a signal emitted by the antenna of the implantable medical device to determine an identifier for the implantable medical device.

Description

[0074] The appended figures will help understand clearly how the invention may be embodied. In these figures, identical references denote similar elements.

[0075] FIG. 1 represents schematically a first example of a medical system comprising a medical device.

[0076] FIG. 2 represents schematically a detail of the electrical circuit of the stent in FIG. 1.

[0077] FIG. 3 represents schematically a second example of a medical system comprising a medical device.

[0078] FIG. 4 represents schematically a third example of a medical system comprising a medical device.

[0079] FIG. 5 shows schematically a detail of the medical device in FIG. 4,

[0080] FIG. 6 represents schematically a fourth example of a medical system comprising a medical device.

[0081] FIGS. 7 and 8 are schematic representations of alternative embodiments of the electrical circuits in FIGS. 1 and 3.

[0082] FIGS. 9 and 10 illustrate schematically an alternative embodiment of the electrical circuit in FIGS. 4 and 5.

[0083] FIGS. 11 and 12 illustrate two examples of electrical circuits having a plurality of measurement lines.

[0084] FIG. 13 represents schematically in perspective a stent provided with sensors.

[0085] FIG. 14 is a flow chart of a method for querying a medical device.

[0086] FIG. 15 represents schematically a medical device identifier comparator.

[0087] Hereinafter in the description, elements that are identical or have an identical function bear the same reference sign in the various embodiments. For the purposes of conciseness of the present description, these elements are not described with regard to each of the embodiments, only the differences between the embodiments being described.

[0088] FIG. 1 illustrates schematically a medical system 10 comprising an implantable medical device 12 and a unit 14, herein single, for querying the medical device 12 and receiving information from said medical device 12. Obviously, units for querying and receiving information may, alternatively, be separate. The medical device 10 may further comprise a unit for processing the information received by the receiving unit, for example a computer.

[0089] The implantable medical device 12 includes a variable impedance 15. The value of this variable impedance 15 is controlled by a control unit not shown, according to the impedance in a measurement circuit 16, connecting particularly the various sensors 22 of the implantable medical device. The implantable medical device 12 further includes an electrical power source, herein a source of electric current formed by the body 18 of the implantable medical device 12. Indeed, under the effect of an electromagnetic field emitted by the querying unit 14, the body 18 of the implantable medical device 12 induces a current. Alternatively, an antenna or armature separate and electrically insulated from the body 18 of the implantable medical device 12 may also be provided, particularly in the case wherein the implantable medical device 12 is not suitable, completely or partially, for having an armature function. In the latter case in particular, an electrical power source for the measurement circuit may include a current-conducting surface of the implantable medical device, suitable for inducing an electric current under the effect of an electromagnetic field. An electric battery or cell may also be provided as an electrical power source for the implantable medical device 12.

[0090] The body 18 of the implantable medical device 12 serves herein also as an emitting antenna, to emit an electromagnetic field outside the body wherein the implantable medical device is implanted. For example, at a constant induced current intensity of the electrical power source, the intensity of this field is directly dependent on the variable impedance 15, according to the impedance in the measurement circuit 16. As such, the intensity or a standard of the electromagnetic field emitted by the body 18 of the implantable medical device 12 (or more generally of the emitting antenna) is dependent on the impedance of the measurement circuit 16. Alternatively, the implantable medical device 12 may include an antenna separate from the body of the implantable medical device or the antenna may be formed by a part at least of the implantable medical device.

[0091] The implantable medical device 12 is for example a stent. The stent is a tubular metal device, preferably meshed, inserted into a natural human (or animal) cavity to keep it open, as described above in the introduction. The stent may for example be made of a metal alloy or polymer material, but other materials may also be envisaged.

[0092] The implantable medical device 12 is provided with variable-impedance sensors 22 according to the physical quantity detected thereby. The term physical quantity denotes herein any property of natural science which may be quantified by measurement or computation, and the different possible values whereof are expressed using any real number or a complex number. A physical quantity includes therefore, for example, a length, an electric current, a voltage, an impedance, a concentration of a chemical element or even the presence and/or concentration of a biological or biochemical element.

[0093] The sensors 22 are distributed on the surface of the implantable medical device. In the particular case of the stent described herein, the sensors 22 may particularly be distributed: [0094] only on the “abluminal” surface of the body of the stent, i.e. the surface opposite the lumen through the stent, intended to be in contact with the wall of the cavity to be kept open but not on the luminal surface; or [0095] only on the luminal surface but not on the abluminal surface; or [0096] both on the luminal and abluminal surfaces; and [0097] on the surfaces connecting the luminal and abluminal surfaces.

[0098] The sensors may be coated with an active agent, for example to limit hyperplasia of the tissues in contact with the implantable medical device, particularly when they are positioned on the abluminal surface of a stent or more generally on the outer surface of an implantable medical device intended to be in contact with the wall of the cavity wherein the medical device is implantable.

[0099] It should be noted that positioning a single sensor, particularly a pressure sensor, on the abluminal surface of a stent, or more generally on the outer surface of an implantable medical device already makes it possible to obtain information relating to the poor positioning of the stent or implantable medical device in the cavity. If the pressure measured is low (i.e. less than a threshold pressure), it is likely that the sensor is not in contact with a wall of the cavity, but rather with blood, for example. In the case where two sensors or more are arranged on the abluminal or outer surface, the information may be obtained with more precision by comparing the values measured by the sensors with one another.

[0100] Preferably, the sensors are arranged at the locations of the implantable medical device, particularly a stent, subject to the least deformations during the fitting of the implantable medical device, in order to avoid damaging the sensors. As such, although FIG. 13 shows a stent 12 with sensors 22a fixed to the vertices of the meshes 120 of the stent 12 and sensors 22c fixed to the mid-point of the sides of the meshes of the stent, it is preferred that all the stents 22c be fixed to the centre of sides of the meshes 120 of the stent 12. The sensors 22a, 22c may be arranged on the inner face or on the outer face of the stent 12. However, it is particularly advantageous to place a pressure sensor in the vicinity of each end of the stent 12, on the inner face of the stent. As such, a difference in pressure between the values measured by these two sensors may be determined which makes it possible to identify the appearance of a blockage inside the stent.

[0101] Each of the sensors may particularly be chosen from: [0102] a shear sensor, [0103] a pressure sensor, [0104] an impedance sensor, [0105] a heat dissipation sensor, [0106] a stress gauge, and [0107] a flow sensor of the “hot wire sensor” type.

[0108] The sensors 22 are variable-impedance sensors, i.e. sensors wherein the impedance varies according to the amplitude or intensity of the physical quantity detected. Hence, in the event of variation of the amplitude of the physical quantity detected by a sensors of the implantable medical device 12, the impedance of this sensor varies in the measurement circuit 16, such that, in the absence of any other variation in the measurement circuit 16, the impedance of the measurement circuit 16 also varies.

[0109] As illustrated, each sensor 22 is associated with a switch 24 suitable for disconnecting from the circuit, in this instance short-circuiting, the sensor 22 with which it is associated. Herein, this is carried out by mounting the switch 24 in derivation (or in parallel) with the sensor 22 with which it is associated. The sensors 22 are herein mounted in series in the measurement circuit 16. For reasons of ease of embodiment and miniaturisation, each switch is herein embodied by a transistor 24, in this instance a silicon MOS-FET transistor, more specifically a depletion-mode, P-channel MOS-FET (or p-MOS) transistor. In further embodiments, each switch or certain switches may be embodied by another type of transistor, particularly by a FET transistor, an enhancement-mode MOS-FET transistor, particularly an enhancement-mode N-channel MOS-FET transistor, by a MEMS (standing for “Micromechanical system”), or by a mechanical switch.

[0110] FIG. 1 further illustrates a system 26 for controlling the switches 24, suitable for successively controlling the opening or closing of the switches 24 according to determined configurations. Herein, the control system 26 includes control modules 28 arranged in series with one another, each control module 28 being suitable for controlling the opening or closing of the switch 24 with which it is associated.

[0111] In this instance, the control system 26 is configured to normally keep the switches 24 closed and to open same successively and then to close them again such that, at each time, a single switch 24 is open.

[0112] For this purpose, each control module 28 is formed herein of a logic circuit, embodied by means of transistors 30, 32, 34, 36, 38, a resistor 40 and a capacitor 42. The resistor 40 and the capacitor 42 introduce a charging time of the capacitor 42 and a discharging time of said capacitor 42 in the logic circuit. During these charging and discharging times, the control module 28 controls the opening of the associated switch 24. The switch 24 is kept closed for the rest of the time, thereby short-circuiting the associated sensor 22.

[0113] More specifically, and as shown in FIG. 2, herein, each control module 28 is embodied by means of three P-channel transistors 32, 34, 38 and two N-channel transistors 30, 36, as follows (only the connections hereinafter are made); [0114] first and second branches 44, 46 of the measurement circuit 16 are connected in parallel, the first branch 44 being the positive power supply terminal and the second branch 46 being the input of the measurement circuit 16 which is powered by a start circuit, not shown in the figures, configured to generate a crenelated voltage pulse during a certain time interval; [0115] the gate of the first transistor 30 and the gate of the second transistor 32 are connected together, as well as to the source of the third transistor 34 and to the second branch 46 of the preceding control module 28, the two transistors 30 and 32 forming a first inverter; [0116] the gate of the fourth transistor 36 and the gate of the fifth transistor 38 are connected together as well as to a terminal of the resistor 40 and to a terminal of the capacitor 42, the two transistors 36 and 38 forming a second inverter; [0117] the source of the first transistor 30, the source of the fourth transistor 36 and a terminal of the capacitor 42 are connected to the ground 48; [0118] the other terminal of the resistor 40, which is not connected to the capacitor 42, is connected to the drain of the first transistor 30 and to the drain of the second transistor 32; [0119] the drain of the fourth transistor 36 and the drain of the fifth transistor 38 are connected together to the second branch 46 of the next control module 28, as well as the gate of the third transistor 34; [0120] the source of the second transistor 32 and the source of the fifth transistor 38 are connected together to the first branch 44 of the preceding control module 28; [0121] the drain of the third transistor 34 is connected to the gate of the transistor 24 having a switch function to short-circuit the sensor 22.

[0122] When the voltage applied at the input of the first inverter is close to zero, therefore less than the threshold voltage of the transistors 30 and 32, the PMOS type transistor 32 is switched to the ON-state, charging the capacitor 42. At the end of the charging thereof, the voltage at the input of the second inverter is greater than the threshold voltage of the transistors 36 and 38, rendering the NMOS type transistor 36 ON. A voltage close to zero is transmitted at the output of the second inverter connected to the gate of the PMOS type transistor 34. The latter is then switched to the ON-state, transmitting a voltage close to zero to the gate of the PMOS type switch 24, which triggers the closing thereof. While a voltage close to zero is applied to the input of the first inverter, the switch 24 is kept closed.

[0123] When a voltage greater than the threshold voltage of the transistors 30 and 32 is applied at the input of the first inverter, the NMOS type transistor 30 is switched to the ON-state, transmitting to the output thereof the ground potential, which triggers the discharging of the capacitor 42. During this discharging, the voltage at the input of the second inverter decreases until it becomes less than the threshold voltage of the transistors 36 and 38, inhibiting the transistor 36 and activating the transistor 38. The latter thereby transmits to the output of the second inverter a potential greater than the threshold voltage of the transistor 34, triggering the inhibition thereof. Consequently, the switch 24 opens. As such, by applying a high positive voltage at the input of the first inverter of the first control module 28, the opening is induced of the switch 24 which is connected thereto, followed by the successive opening of the switches 24 connected to the subsequent control modules 28. The start circuit, not shown, powering the input 46 of the first module is configured to generate a crenelated voltage pulse for a time interval τ=RC. The trailing edge of this pulse induces the closing of the switch of the first module after a time equal to τ. The voltage pulse is propagated from one input 46 to another, such that the trailing edge of this pulse at the input of a module n corresponds to the leading edge of the pulse at the input of the module n+1. As such, in this instance, during the propagation of the pulse, all the switches are closed except one.

[0124] With such a control system, the voltage at the terminals of the measurement circuit 16, which is equal to the sum of the voltages at the terminals of each of the sensors mounted in series in the measurement circuit, exhibits successive peaks which are representative of the voltage at the terminals of each of the sensors. To each of the successive peaks, each representative of the voltage at the terminals of a sensor 22, corresponds an intensity of the electromagnetic fields emitted by the body 18 of the implantable medical device 12 having an emitting antenna function.

[0125] In FIG. 1, the presence of a rectifier 56 as well as of an alternating current generator 58 in the implantable medical device 12 is observed. They make it possible respectively to supply the control circuit 26 with direct current and the measurement circuit 16 with a current having a frequency distinct from, particularly less than, the frequency of the induced current in the antenna 18. This may be useful as the frequency of the induced current is dependent on the electromagnetic field emitted by the unit 14 said frequency being preferably chosen such that the electromagnetic wave is absorbed to a low degree by the tissues traversed. The use of such a frequency in the measurement circuit could impede the precision of the measurements made.

[0126] The measurement circuit 16 is moreover completed in FIG. 1, by a combination of sets of an impedance 60, that is fixed and known, and a switch 24, controlled by a control module 28, as is the case for the switches 24 associated with the sensors 22. This combination of known impedances makes it possible to identify the implantable medical device queried, for example by associating a combination of impedances 60 that are unique and known to each implantable medical device 12. This particularly useful in the case where a plurality of such implantable medical devices have been implanted in the body of the same patient. Some electromagnetic field peaks measured are then used to identify the implantable medical device 12, the other peaks to determine the values measured by each of the sensors of the implantable medical device 12 identified. For example, the first electromagnetic field peaks measured may be used for identifying the implantable medical device 12 and the subsequent peaks for determining the values measured by each of the sensors of the implantable medical device 12 identified. Furthermore, these impedances being known, they are also suitable for calibrating the medical system 10. In other words, these known impedances make it possible to quantify more accurately the values measured by the different sensors of the different implantable medical devices.

[0127] Alternatively, according to the embodiment represented partially and schematically in FIG. 15, the medical device may include a comparator 94 for comparing an identifier ID1 emitted by the querying unit 14, with a binary code ID2 associated with the combination of impedances 60 present on the electrical circuit, this binary code being derived for example from the output of the analogue/digital converter 80, or an identifier saved in a memory in the stent. The medical device may then be configured to only respond to the query by the querying unit if the comparison is positive. Advantageously, the identification may be carried out iteratively, the querying unit merely emitting one identification value at a time, each stent wherein the value corresponding of the identifier not corresponding being disabled—i.e., herein, not electrically powered—for a time suitable for identifying the only stent corresponding to the unique identifier and carrying out the measurements using different sensors in this medical device.

[0128] FIG. 3 represents a second example of a medical system 100. This medical system is substantially identical to that described above. However, in this embodiment, in the measurement circuit 16 of the implantable medical device 12, the known impedances 60 and the sensors are mounted in series with the switch 24 which is associated therewith, the sets formed of an impedance 60 or a sensor 22 and a switch 24 being mounted in parallel (or in derivation) with respect to one another. Hence, the control modules 28 being identical to those described above, the electromagnetic field emitted following the creation of an induced current, corresponds to the sum of all the impedances 60 and of all the sensors 22, minus one, each of the impedances 60 and the sensors 22 being disconnected from the circuit, in this instance disconnected, successively.

[0129] Alternatively, obviously, it is possible to embody a control module 28 having a different operation, which controls the closing of the switch 24 during a time interval only, the switch 24 being open the rest of the time. Such an operation may also be obtained by retaining the control module 28 as described above and by replacing the depletion-mode MOS-FET transistors used as switches 24 by enhancement-mode MOS-FET transistors.

[0130] FIGS. 4 and 5 illustrate a further example of a medical system 200. According to this example, the control of the switch 24 for disconnecting from the circuit the sensor 22 or a known impedance 60 is implanted directly in a module 62 also comprising the known impedance 60 or the sensor 22, and the switch 24, herein embodied by a transistor. As for the other examples described above, a resistor 40 and a capacitor 42 are used to control the switch 24 such that it disconnects from the circuit the impedance 60 or the sensor 22 except during a charging time interval of the capacitor 42. Charging the capacitor 42 activates the transistor 66 of the next module, inducing the charging of the corresponding capacitor 42. Once charged, the capacitor 42 inhibits the associated transistor 24, triggering the disconnection from the circuit of the impedance 60 or the sensor 22 which is connected thereto.

[0131] Herein, as represented in FIG. 5, each module 62 is embodied as following: [0132] the first and second branches 44, 46 are in parallel; [0133] a terminal of the sensor 22 or of the impedance 60 is connected to the ground 48; [0134] the other terminal of the sensor 22 or of the impedance 60 is connected to the drain of the transistor 24; [0135] the gate of the second transistors 66 is connected to the second branch 46 of the preceding module 62; [0136] the drain of the second transistor 66 is connected to the first branch 44 of the preceding and next modules 62; [0137] the source of the second transistor 66 is connected to the source of the transistor 24 and to a diode 64; [0138] the other terminal of the diode 64, which is not connected to the transistors 24, 66, is connected to a terminal of a fixed impedance 40; [0139] the other terminal of the impedance 40, which is not connected to the diode 64, is connected to the gate of the transistor 24, to a terminal of a capacitor 42, connected by the other terminal thereof to the ground 48, and to the second branch 46 of the next module 62.

[0140] As for the preceding examples, due to the configuration of the modules 62, each sensor 22 and impedance 66 is successively connected to the antenna 18 in order to be powered, the other sensors 22 and impedances 66 being for their part disconnected.

[0141] Finally, FIG. 6 represents a fourth example of an embodiment of a medical system 300. This medical system 300 is distinguished from the preceding example 200, in that the measurement circuit 16 is directly connected to the antenna 18 for the emission of an electromagnetic field, without the intermediary of a separate variable impedance (the measurement circuit 16 itself having a variable impedance) and of a unit for controlling this variable impedance according to the impedance of the measurement circuit 16. The electrical circuit on the medical device 12 is then particularly simplified.

[0142] Obviously, it is possible to conceive a structure where the measurement circuit 16 is connected directly to the antenna, the implantable medical device also comprising a control circuit associated with this measurement circuit and as described for example with regard to FIGS. 2 and 3.

[0143] In practice, in the embodiments described above, each module may particularly by embodied in the following form. Two measurement electrodes, for example of 60×60 μm.sup.2, made of an electrically conductive material, for example of polymer material or of metal alloy, preferably biocompatible, are deposited on an electrically insulating, biocompatible polymeric substrate (for example parylene). The electrical components of the control system and the switch are implanted in the polymeric substrate.

[0144] The medical systems described above are suitable for carrying out a querying method 500 of the implantable medical device 12, as shown by the flow chart in FIG. 14.

[0145] This method 500 includes a first step 502 consisting of powering the measurement circuit 16. Preferably, this power supply is carried out by an induced current in an antenna or in the body of the implantable medical device 12 when the latter is configured to generate an induced current. This makes it possible to power the measurement circuit 16 only when a measurement is made.

[0146] The method 500 is continued by a step 504 consisting of activating the system for controlling the implantable medical device so that it successively controls the opening of the closing of each of the switches of the implantable medical device, according to determined configurations. It should be noted herein that within the scope of the examples described with regard to the figures, this activation is carried out simultaneously with the power supply of the measurement circuit 16, by induction, in response to the emission of an electromagnetic field by the querying device. The method 500 then includes a step 506 for identifying the queried medical device. This step may, alternatively, be carried out before electrically powering the measurement circuit.

[0147] The identification may be carried out either in the medical device per se, when the latter is provided with a comparator to compare an identification signal emitted by the querying unit with a unique identifier of the medical device. As indicated above, this identifier may take the form of a combination of known impedances in the medical device and/or in each measurement line of the medical device. The identification may be carried out iteratively, the querying unit merely emitting one digit of the identifier at a time, each of the medical devices wherein the identifier does not correspond to this digit being temporarily deactivated (i.e., in the example studied, not electrically powered).

[0148] Alternatively, the identification is carried out in the processing unit, the signals emitted by the antenna 18 being interpreted by the processing unit to determine the combination of the impedances of the medical device and/or of the measurement line queried. A processing unit may be used to determine the value measured by each sensor and the implantable medical device that responded to the query, particularly if the controlled configurations of the measurement circuit are more complex.

[0149] To do this, the processing unit may particularly be suitable for conducting Fourier analyses of the measured signals of electromagnetic fields emitted by the antenna of the implantable medical device, comparing the signals received (optionally processed) to previously measured signals and inferring therefrom the values measured by the various sensors of the implantable medical device, one location being suitable for being determined for each of the values measured.

[0150] If the identification is negative, the medical device is temporarily deactivated, in the step 508.

[0151] If the identification is positive, the method 500 is continued then by a step 510 consisting of measuring the electromagnetic field emitted by the antenna of the implantable medical device. This measurement is made over a relatively long time so that the control system will have been able to control a relatively large number of different configurations of the measurement circuit so that the measurement makes it possible to determine the value measured by each of the sensors 22 of the implantable medical device 12. Throughout the measurement step, the antenna 14 preferably emits a constant electromagnetic field to maintain the power supply of the measurement circuit 16 and the activation of the control system 26.

[0152] Preferably, each configuration corresponds to the scenario where all the sensors or impedances of the measurement circuit are disconnected from the circuit, except one. As such, on the basis of the electromagnetic field measured, it is possible to determine first of all the implantable medical device that responded to the query. Indeed, the first peaks measured in the electromagnetic field emitted by the antenna correspond to fixed impedances, the combination whereof makes it possible to identify the implantable medical device. These magnetic fields measured may also be suitable for calibrating the system since the magnetic fields measured correspond to known impedances of the measurement circuit. Finally, the subsequent magnetic fields make it possible to determine the values measured by each of the sensors distributed on the implantable medical device.

[0153] When elements 60A are envisaged between the sensors 22, the corresponding magnetic fields emitted may be used to calibrate the following and/or preceding emitted signal, which originates from a measurement by a sensor 22.

[0154] Once all the sensors 22 of the medical device 12 have been queried, the electrical power supply of the electrical circuit is switched off and the electrical circuit of the medical device 12 is deactivated.

[0155] It should be noted herein that the method described may be used with any type of variable-impedance sensor according to the physical quantity detected thereby. It should also be noted that the sensors distributed on the implantable medical device may be of different types, i.e. they may detect different physical quantities.

[0156] The method described above may particularly be used to determine whether the implantable medical device is suitably implanted (i.e. positioned) in the natural cavity that it is supposed to keep open, in particular, if it is indeed in contact with the wall of the cavity. Indeed, the effect of a stent, for example but this is true for most implantable medical devices, is markedly reduced if the latter is not bearing on the wall of the cavity (particularly of the vein or the artery) wherein it is inserted.

[0157] For example, by placing pressure sensors on the abluminal surface of the stent, i.e. on the surface opposite the lumen through the stent, that which is intended to be in contact with the wall of the cavity wherein the implantable medical device is received, the method described above makes it possible to determine whether each of these sensors is in contact with the wall, since it makes it possible to determine the pressure measured by each of the sensors. Obviously, this function for determining the suitable position of the stent may be combined, that is to say that sensors, for example of pressure, may be arranged on the abluminal surface of the stent and sensors, optionally of another physical quantity, may be arranged on the luminal surface of the stent.

[0158] Alternatively, sensors of the same physical quantity are distributed on the abluminal surface and on the luminal surface, substantially at the same position on the stent or implantable medical device. In other words, sensors of the same physical quantity are arranged at the same point of the stent, on either side of the stent body. The comparison of the values measured by each of these stent pairs also makes it possible to obtain indications of an incorrect position of the stent in the cavity. In particular if the sensor on the abluminal surface, which should therefore be in contact with a wall, measures a substantially identical value to the sensor on the luminal surface, which is in contact with the blood, it is likely that the sensor on the abluminal surface is in fact in contact with blood also, not with a wall. It is therefore likely that the stent is poorly positioned in the cavity.

[0159] Obviously, the method described above may be suitable for obtaining numerous other items of information.

[0160] In particular, it may be suitable for determining whether a sensor arranged on the luminal or abluminal surface of the stent or, more generally, on a surface of an implantable medical device, particularly on a surface of the implantable medical device in contact with a wall of the cavity wherein the medical device is implanted or on a surface of the implantable medical device intended to be in contact with the blood, is optionally coated with endothelial or smooth muscle tissue.

[0161] It may also be suitable for determining the composition of the tissue coating the sensors distributed on the implantable medical device (particularly on the luminal surface or on the abluminal surface of a stent) for example by Electrical Impedance Spectroscopy (EIS), particularly by applying currents of separate frequencies in the measurement circuit.

[0162] The electrical circuit 10A in FIG. 7 is an alternative embodiment of the circuit in FIG. 1.

[0163] The electrical circuit 10A firstly includes an analogue/digital converter 80 situated between the electrical measurement circuit 16 and the variable impedance 15 connected to the antenna 18 in the emitting circuit. This analogue/digital converter 80, which may also be used in the electrical circuit 10 in FIG. 1 makes it possible to increase the range of signals which may be emitted by the antenna 18. This converter 80 also makes it possible to enhance the signal-to-noise ratio of the measurements made.

[0164] Moreover, the electrical circuit 10A is distinguished from that in FIG. 1 by the presence of an element 60A of fixed and known impedance, for example a resistor, between the sensors 22. As for the impedances 60, the element 60A is associated with a switch 24 controlled by a control module 28 in a module 62A. The impedance of this element 60A is preferably chosen such that the sensors 22 cannot attain this impedance value. For example, the impedance of the element 60A is less than 90% of the minimum impedance suitable for being attained by sensor 22 and/or greater than 110% of the maximum impedance suitable for being attained by a sensor 22. As such, between two emitted signals relative to a measurement by a sensor 22, a transition signal, easily identifiable, is emitted. It is easier, as such, to distinguish between two successive measurements, separated by a signal of expected form. Moreover, the presence of this element 60A between the sensors 22 may be suitable for calibrating the following and/or preceding sensor 22. The measurement is therefore more precise. Obviously, further configurations may be envisaged. In particular, it is possible to envisage an element 60A at the start of a line only, all the n sensors 22, n being a natural integer different to zero, or even an irregular distribution of the elements 60A on the measurement line.

[0165] FIG. 8 represents an alternative embodiment 100A of the electrical circuit 100 in FIG. 3, with an analogue/digital converter 80 and elements 60A of known and fixed impedance, such as the electrical circuit 10A. The advantages of these modifications are the same as within the scope of the electrical circuit 10A in FIG. 7.

[0166] The same applies for the electrical circuit 200A illustrated by FIGS. 9 and 10 and obtained by making the same modifications to the electrical circuit 200 in FIGS. 4 and 5.

[0167] It should be noted herein that the presence of the elements 60A of known and fixed impedance and of the analogue/digital converter 80 are independent. Embodiments may be envisaged not involving one of the two among the analogue/digital converter 80 and the elements 60A of known impedance.

[0168] In FIG. 11, an electrical diagram of an alternative electrical circuit 10B of the electrical circuit 10 in FIG. 1 has been represented. This electrical diagram 10B is distinguished from the electrical circuit 10 in FIG. 1 in that it includes a plurality of measurement lines 90, mounted in parallel, where the electrical circuit 10 in FIG. 1 merely includes a single line. Herein, the measurement lines 90 are identical to the single line represented in FIG. 1. The measurement circuit 16 includes however line selectors 92, to carry out the measurement in each of the lines independently from the other lines 90, particularly each line in succession from one another. The line selectors 92 may adopt a substantially identical form to the control modules 28, thereby supplying each line 90 with current, successively.

[0169] In the example shown, an analogue/digital converter 80 is also provided between the parallel branches formed by the measurement lines 90 and the variable impedance 15.

[0170] The electrical circuit 10C illustrated in FIG. 12 is similar to the electrical circuit 10B in FIG. 11. It is essentially distinguished by the presence of an analogue/digital converter 80 on each of the measurement lines 90 in parallel.

[0171] It should be noted that it is also possible to envisage electrical circuits with a plurality of measurement lines 90 on the basis of the electrical circuits 100 and 200 in FIGS. 3 and 4.

[0172] It is also possible to envisage elements 60A of known and fixed impedance between each of the sensors on each of these lines or on certain lines only. It is then possible to identify the line wherein the measurement is made at each time by choosing unique combinations of impedances 60 at the start of the line 90 for each line 90.

[0173] In the scenario where the electrical circuit 10B, 10C includes a plurality of measurement lines, it has been determined that it is particularly advantageous that the measurement lines extend on the medical device 12, particularly on the stent 12 in imbricated coaxial helices. In other words, the measurement lines extends in parallel along helices wound around one another. Indeed, this makes it possible to minimise the distance between sensors of different lines. This is particularly advantageous because if a sensor 22 of a line 90, or even the entire line 90 is defective, the missing value(s) may be better approximated by the values measured with the other measurement line(s), of which one or a plurality of sensors are situated in the vicinity. The device 12 thereby gains in robustness, which is particularly advantageous when it is implanted in a patient's body.

[0174] It should be noted that the electrical circuits described are suitable for determining for each sensor of the electrical circuits, the value measured thereby. The position of the sensors on the medical device, particularly on the stent, being known, it is possible to determine a model representing in real time, the progression of the physical parameters measured on the medical device. As such, a practitioner may obtain real-time information. This information may particularly relate to the correct positioning of the medical device, particularly of the stent, in a cavity of the human body. Representing the pressures measured by pressure sensors arranged on the outer surface of the medical device, particularly of the stent, can enable the practitioner to determine whether this medical device is correctly implanted or not: a measured pressure that is too low, for example, may indicate that the stent is not in contact with the wall of the cavity receiving same.

[0175] The processing unit of the medical system described above, comprising for example an electronic control unit and a screen, or a computer, may be suitable for determining a real-time model, for example a 3D model, based on the values measured and displaying the model on the screen. The values between the measurement points may, in this case, be approximated, particularly by convolution according to the distance to the closest measurement points.

[0176] Various visual and/or acoustic signals may be emitted by the processing unit, in the scenario where at least one measured value does not meet expectations. The visual signals may particularly be suitable for identifying on the model shown, the sensors 22 for which the measured values are not conforming.

[0177] Alternatively, the processing unit may process the digital values measured, compare them to expected value ranges and display as an output in a different manner, the points where the measurement is within the ranges and the points where the measurement is not within the ranges, for example by using different display colours.

[0178] The visual signals complete the display of the model described above.

[0179] The invention is not restricted solely to the examples of embodiments described above with regard to the figures, by way of illustrative and non-restrictive examples.

[0180] In particular, the implantable medical device may be chosen from the group comprising: [0181] a heart valve, [0182] a cardiac stimulator, [0183] a cochlear implant, [0184] a throat implant, [0185] an orthopaedic implant, [0186] a brain implant, [0187] a retinal implant, [0188] a catheter, or [0189] a cellular tissue (“tissue-engineered construct”).

[0190] Alternatively, the medical device may not be implantable. It can then, in particular, be applied on a part of the human body. The medical device may in this case take the form of a dressing, bandage or strip to be applied onto a patient's skin. The medical device may also take the form of a contact lens to be placed on a patient's cornea.

[0191] Finally, according to a further alternative embodiment, the medical device may be neither implantable in the human body, not applicable thereon.