EP2739202A1 - Procédé et dispositif pour la transmission de données de détection entre un capteur implantable et un appareil extérieur de traitement des données - Google Patents

Procédé et dispositif pour la transmission de données de détection entre un capteur implantable et un appareil extérieur de traitement des données

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Publication number
EP2739202A1
EP2739202A1 EP12748173.7A EP12748173A EP2739202A1 EP 2739202 A1 EP2739202 A1 EP 2739202A1 EP 12748173 A EP12748173 A EP 12748173A EP 2739202 A1 EP2739202 A1 EP 2739202A1
Authority
EP
European Patent Office
Prior art keywords
sensor
unit
data
energy storage
storage unit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP12748173.7A
Other languages
German (de)
English (en)
Inventor
Karlheinz Göhler
Peter Peitsch
Reinhard Jurisch
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Raumedic AG
Original Assignee
Raumedic AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Raumedic AG filed Critical Raumedic AG
Publication of EP2739202A1 publication Critical patent/EP2739202A1/fr
Withdrawn legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/07—Endoradiosondes
    • A61B5/076—Permanent implantations
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0015—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by features of the telemetry system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0015—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by features of the telemetry system
    • A61B5/002—Monitoring the patient using a local or closed circuit, e.g. in a room or building
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0031—Implanted circuitry
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/90—Identification means for patients or instruments, e.g. tags
    • A61B90/98—Identification means for patients or instruments, e.g. tags using electromagnetic means, e.g. transponders
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0204—Operational features of power management
    • A61B2560/0214—Operational features of power management of power generation or supply
    • A61B2560/0219—Operational features of power management of power generation or supply of externally powered implanted units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0242—Operational features adapted to measure environmental factors, e.g. temperature, pollution
    • A61B2560/0247—Operational features adapted to measure environmental factors, e.g. temperature, pollution for compensation or correction of the measured physiological value
    • A61B2560/0257—Operational features adapted to measure environmental factors, e.g. temperature, pollution for compensation or correction of the measured physiological value using atmospheric pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/08—Sensors provided with means for identification, e.g. barcodes or memory chips
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/03—Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs
    • A61B5/031—Intracranial pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14553—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4869—Determining body composition

Definitions

  • the invention relates to a method and a device for the transmission of sensor data of an implantable sensor to an external data-processing device.
  • Telemetry sensor devices with implantable sensors are known from the prior art, for example from US 5,704,352 A, US Pat. No. 6,083,174 A and WO 2010/107 980 A2.
  • Such telemetry sensor devices may be adversely affected by environmental conditions. Often, therefore, in the known telemetry sensor devices for the transmission of energy to the implantable sensor, a magnetic or electromagnetic field with a minimum strength is used, which may have negative effects on the transmission of sensor data from the implantable sensor to the external data processing device. Some attempts have been made in the prior art to solve this problem with shields, which either does not succeed adequately or only with disproportionately great effort.
  • the determined sensor data should be largely independent of the distance and relative position as well as the environmental conditions of the implantable sensor and thus enable reproducible measurements. This object is achieved by a method having the features specified in claim 1 and by a device having the features specified in claim 5.
  • the transmission method such that no high-frequency radiation occurs during the actual measurement.
  • the high frequency field can not interfere with the measurement process.
  • the measuring data recorder is supplied by the energy storage unit of the implanted sensor.
  • the result is an RF interference-free measurement, which has a corresponding high signal-to-noise ratio.
  • implantable sensors sensitive sensors generating an analogue useful signal can be used.
  • the same wireless, in particular inductive link can be used. This leads to a compact construction of the device for carrying out the transmission method.
  • the energy supply device can be part of the external data processing device.
  • the external data processing device can be designed as a pure measurement data display without further processing. Alternatively, the external data processing device can further process the received measurement data.
  • the transmission method can be used in telemetry measurement, in particular in patient monitoring. In particular, the radiation of the high-frequency energy carrier signal can be terminated when the energy required for the measurement is reached. In this case, there is no unnecessary energy conversion in lost heat. A disturbance of the measuring operation or a reduction of the well-being of the patient due to unnecessarily registered waste heat is then avoided. the.
  • further data for example identification and / or calibration data, can also be transmitted during the transmission step from the transmitter unit of the implantable sensor to the transmitter / receiver unit of the external data processing unit.
  • a terminating irradiation of the high-frequency energy carrier signal may occur depending on the transmission distance between the implantable sensor and the external data-processing device. This transmission distance can be measured in a known manner. At a small transmission distance, the radiation of the high-frequency energy carrier signal can be terminated at an earlier time than at a larger transmission distance.
  • Monitoring according to claim 2 ensures that no undesired disturbing influences on the measurement result due to insufficient energy supply of the measuring data recorder.
  • the monitoring can be done by voltage comparison.
  • a conversion according to claim 3 allows a virtually trouble-free data transmission from the implanted sensor to the external data-processing device.
  • the conversion or else the transfer of the A / D-converted and temporarily stored data can be carried out after a resumption of the RF irradiation, that is, while the implanted sensor is being charged again by irradiation of the RF field.
  • a resumption of the RF radiation according to claim 4 results in that an RF field-free operating phase of the implantable sensor during the measurement data recording can be kept very short. This reduces the requirements for the energy storage unit of the implantable sensor, which can be made correspondingly compact. Transferring the Sensor data can then take place with the aid of an energetic support by the radio frequency energy carrier signal irradiated during the transmission.
  • the transmission of the measured sensor data can be done by means of passive FID technology.
  • the measured data recorder can be designed as a pressure sensor, in particular as an intracranial pressure sensor. Other sensor units for recording physiological measurement data can also be used.
  • the external data processing device has a control unit for controlling the transmission method. In particular, the control unit is used for starting and performing a measuring operation.
  • a capacitor according to claim 6 is a simply constructed energy storage unit of the implantable sensor. In particular, a tantalum capacitor can be used.
  • a monitoring unit according to claim 8 can be designed as a voltage comparator. The advantages of the monitoring unit have already been explained in connection with the transmission procedure.
  • start unit By means of a start unit according to claim 9 it is ensured that a measurement with the measuring data recorder only begins when the RF field reliably shut off.
  • the start unit only transmits a signal for starting the measurement when the RF field has ended reliably.
  • a voltage sensor as a start unit according to claim 10 enables a direct detection of the termination of the RF field. It is impossible that a start signal is triggered as long as the RF field exists.
  • a time sensor as a start unit according to claim 1 1 allows easy triggering of the start signal.
  • FIG. 1 shows schematically a device for transmitting sensor data of an implantable sensor to an external data-processing device
  • FIG. 2 is a flowchart of a sensor data transmission method using the apparatus of FIG. 1.
  • a transmission device 1 serves to transmit sensor data of an implantable or implanted sensor 2 to an external data-processing device 3.
  • the implanted sensor 2 is, for example, a brain parameter sensor.
  • the implanted sensor 2 is a sensor transponder.
  • the implanted sensor 2 has a measurement data recorder 4 for acquiring physiological measurement data, for example, for recording an intracranial pressure, a blood or tissue oxygen content, a blood or tissue composition, a water content or a temperature.
  • the measuring data recorder 4 is designed as a piezoresistive pressure sensor. It is also conceivable to provide a capacitive pressure sensor instead of the piezoresistive pressure sensor.
  • the measured data recorder 4 can also be designed as a strain sensor.
  • the implanted sensor 2 can also have a plurality of measurement data receivers in the manner of the measurement data recorder 4, which can record, for example, different measurement data.
  • the external data processing device 3 may include an air pressure sensor, not shown.
  • the air pressure sensor makes it possible to take account of the air pressure of the environment when determining an implant pressure by means of a pressure sensor as the measurement data recorder 4. This makes it possible to carry out the pressure measurement in the implanted sensor 2 independently of possible air pressure fluctuations in the environment of use of the implanted sensor 2.
  • the measuring data recorder 4 is connected via a bidirectional signal line 5 to a sensor circuit 6, via which on the one hand the measuring data recorder 4 is controlled and to which the recorded measuring data are transmitted by the measuring data recorder 4.
  • the sensor circuit 6 serves to control the measuring data recorder 4, for example via a constant current source or a constant voltage.
  • the signal line 5 can have one line, two lines or a larger number of lines.
  • the measurement data recorder 4 as piezoresistive pressure sensor, two lines serving the measurement data transmission and
  • two supply or supply lines may be provided which connect the measuring data recorder 4 to the sensor circuit 6.
  • Other types of sensor can manage with the sensor circuit 6 over a smaller number of lines, for example, with two of the measurement data transmission lines serving.
  • the sensor circuit 6 is connected to an energy storage unit 8 of the implanted sensor 2 via a power supply line 7. Via the bidirectional signal line 5, a power supply of the measuring data recorder 4 is ensured via the sensor circuit 6.
  • the sensor circuit 6 may comprise further circuit parts, for example an analog multiplexer for switching between a plurality of measuring data transducers, at least one analog amplifier for signal conditioning or at least one analog / digital converter.
  • the energy storage unit 8 is a capacitor, in particular a tantalum capacitor.
  • the capacitor may have a capacitance in a range of 10 ⁇ to 1000 ⁇ .
  • the value of the capacitance of the capacitor can be adjusted depending on the application.
  • the current consumption of the implantable sensor 2 to be determined may determine a preferred value of the capacitance of the capacitor.
  • the power consumption should be as low as possible.
  • the capacitor has a capacity of 100
  • the energy storage unit 8 is therefore arranged in particular according to a voltage limiter and according to a voltage stabilizer of the transmitter unit 13. This ensures that stored in the energy storage unit 8 electrical energy is not discharged again against a charge. An unwanted discharge is due to the arrangement of the Energy storage unit 8 reliably prevented. Such a discharge would basically be conceivable via the resonant circuit, provided that the voltage limiter and the voltage stabilizer were not arranged in front of the energy storage unit 8.
  • the arrangement of the energy storage unit 8 behind the voltage stabilizer ensures the possibility of using a voltage sensor 36 as the starting unit.
  • the capacitance of a capacitor of the voltage sensor 36 is smaller than the capacity of the energy storage unit 8.
  • the capacity of the energy storage unit 8 is at least a factor of 100 greater than the capacitance of the capacitor of the voltage sensor 36.
  • the ratio of the capacitance Energy storage unit 8 to the capacitance of the capacitor of the voltage sensor 36 at least 150, in particular at least 200 and in particular at least 300. This ensures that when switching off the RF field on the one hand, the voltage at the voltage sensor 36 drops at a sufficient speed.
  • the voltage drop at the voltage sensor 36 is fast and in particular with a time delay of at most 1 s.
  • the voltage of the energy storage unit 8 during the RF field-free measurement is substantially constant and in particular does not fall.
  • the voltage of the energy storage unit 8 drops to at most 85% of an output voltage value of the energy storage unit 8, in particular to at most 90% and in particular to at most 95%.
  • the sensor circuit 6 is in a bidirectional signal connection via a signal line 9 with a microcontroller 10, that is to say a process computer unit.
  • a microcontroller 10 Part of the microcontroller 10 is an analog / digital Converter 1 1.
  • the latter converts the recorded by the Meß stylistauf disrupt 4 analog measurement or sensor data, which are fed via the sensor circuit 6 to the micro-controller 10, in further to be transmitted digital sensor data.
  • the A / D converter 1 1 may also be part of the sensor circuit 6.
  • a further signal line 12 is the micro-controller 10 with a transmitter unit 13 of the implanted sensor 2 in the form of an RFID interface in bidirectional signal connection.
  • the transmitter unit 13 is connected via supply line 14 to the energy storage unit 8 in signal connection and serves to charge the energy storage device 8 from part of the radiated over the external data processing device 3 high-frequency energy.
  • a monitoring line 15 is a monitoring unit 16 with the micro-controller 10 in signal communication.
  • the monitoring unit 16 is a monitoring unit 16 with the micro-controller 10 in signal communication.
  • the monitoring unit 16 serves to monitor a power supply of the microcontroller 10, the sensor circuit 6 and the measuring data recorder 4 by the energy storage unit 8.
  • the monitoring unit 16 is designed as a voltage comparator.
  • the external data processing device 3 has a transmitter / receiver unit
  • control unit 19 can, for example, have a real-time clock to store stored data. - To provide deleted measurement data with a unique time signal, in particular with a time stamp.
  • control unit 19 may include components that allow, for example, calculation of measured values, their display, their monitoring and their storage.
  • the energy storage unit 8 is designed as a battery and / or as an accumulator.
  • the implanted sensor 2 can have a real-time clock in order to provide stored measurement data with a unique time signal, in particular with a time stamp.
  • the implanted sensor 2 may have a memory unit for storing the measured measured values. In this case, the implanted sensor 2 would be at least temporarily self-sufficient, in particular independent of the external device 3, and could in particular be used without an RFID power supply.
  • Antennas of the transmitter unit 13 and the transmitter / receiver unit 17 are designed as coils, which are connected as a resonant circuit.
  • the transmitter unit 13 serves for rectification, limitation and stabilization of a voltage induced in the RF field feed and for demodulation and modulation of the measured data and possibly other data.
  • a rectifier for rectification, limitation and stabilization, a rectifier, a voltage limiter or a voltage stabilizer can be integrated in the transmitter unit 13.
  • the voltage sensor 36 is provided in the transmitter unit 13, which measures the voltage of the high-frequency field.
  • the voltage sensor 36 can also be arranged externally of the transmitter unit 13.
  • the voltage sensor 36 is designed as a capacitor and has a capacitance of 10 nF. This makes it possible for the capacitor, which is arranged in particular after the rectifier in the transmitter unit 13, to be able to follow the HF field quickly, ie with a short time delay of at most 1 ms.
  • a time sensor 37 may be provided.
  • the voltage sensor 36 and the time sensor 37 are connected via the signal line 12 to the micro-controller 10.
  • the voltage sensor 36 is arranged in particular according to a voltage limiter, which causes a decoupling of the high-frequency oscillation circuit and the rectifier.
  • the control unit 19 controls the transmission method described below with reference to FIG.
  • the control unit 19 outputs via a control pulse the signal for a switch-on step 20 for switching on an HF field that is generated by the power supply unit 18.
  • the RF field has a frequency of 13.56 MHz. Another carrier frequency for the RF field is possible.
  • a radiofrequency (RF) energy carrier signal is then irradiated via a wireless link, wherein the transmitter / receiver unit 17 is used as an RF transmitter and the transmitter unit 13 as an HF receiver.
  • the energy storage unit 8 of the implanted sensor 2 is charged in a charging step 22.
  • the charging step 22 at least a part of the energy contained in the high-frequency energy carrier signal is stored in the charging step Energy storage unit 8.
  • the charging time during the charging step 22 can be about 2 s.
  • the transmission unit 13 sends in a return step 23 to the external data processing device 3 the information that the energy storage unit 8 is loaded.
  • the state of charge of the energy storage unit 8 can be monitored via the monitoring unit 16.
  • the charging step 22, that is to say the irradiation of the high-frequency energy carrier signal, can take place during a fixed period of time.
  • a reading step 24 a reading and optionally a writing of identification data of the implanted sensor 2, for example an ID number, an operating status, an operating version and / or calibration data takes place.
  • ID identification
  • This ensures that data transmission takes place only with a desired sensor 2, which can be unambiguously identified, for example, via an identification (ID) number.
  • ID identification
  • a data flow takes place from the transmitting unit 13 via the connecting link 21 to the transmitter / receiver unit 17. If a reading of data also takes place during the reading step 24, this is done in the opposite way.
  • the control unit 19 in a transmission step 25 outputs a start signal for carrying out a process sequence that includes a sensor measurement with the measurement data recorder 4.
  • This start signal is in turn via the link 21 to the implanted sensor 2 transmitted.
  • the measurement ie the measurement data acquisition, is initialized by the microcontroller 10.
  • the initialization of the measurement may take, for example, 50 ms.
  • the microcontroller 10 outputs the information that the measurement is initialized. This initialization signal is transmitted via the link 21 to the external data processing device 3.
  • the irradiation of the high-frequency energy carrier signal is terminated in a switch-off step 28 by corresponding control of the energy supply unit 18 via the control unit 19.
  • the steps 24 to 27 can thus still be carried out during the charging process by the radiofrequency radiation.
  • Energy carrier signal expire. About 10 microseconds after switching off the high-frequency energy carrier signal by the power supply unit 18, the high-frequency field is no longer present.
  • the external data-processing device 3 transmits a switch-off signal to the implanted sensor 2 via the connecting path 21.
  • the turn-off signal is caused in particular by the voltage sensor 36, which detects a change in the RF field and transmits this change of the RF field to the micro-controller 10.
  • this switch-off signal is detected and processed by the sensor circuit 6 of the implanted sensor 2.
  • the measuring process can be started after waiting for a fixed period of time.
  • the fixed time duration can be in the range from 1 ms to 10 ms and in particular 100 s.
  • the time sensor 37 receives the switch-off signal of the external data-processing device 3 and automatically starts a time measurement. The timekeeping is finished when the fixed time is reached. After the fixed period of time, the time sensor 37 transmits a measurement start signal.
  • the voltage sensor 36 and the time sensor 37 in combination.
  • the method is more reliable feasible. It is conceivable, for example, that the measurement only begins when both sensors have transmitted a start signal. The trouble-free measurement is then more reliable possible. It follows after the actual measurement process, ie the detection of
  • the microcontroller 10 is then placed in a state of rest. A total current consumption of the circuit of the implanted sensor 2 and also a measuring time are kept as low as possible.
  • This precisely defined period of time may be 50 ms.
  • the switch-on step 31 in a reloading step 32, the energy-storage unit 8 is recharged via the connecting link 21. This reloading step 32 is optional.
  • the information is sent back that the energy storage unit 8 has been charged.
  • the return step 33 is executed analogously to the return step 23. Alternatively, charging of the energy storage unit 8 may take place again during a predetermined, fixed period of time.
  • the control unit 19 After receiving the loading information via the return step 33 or after waiting for the fixed period of time, the control unit 19 initiates a transfer of the measured and converted measurement data via the link 21. This is done in a read-out step 34 in which the digitally converted measurement data and possibly other status information on the verb indungs line 21 are sent over the implanted sensor 2 towards the external data processing device 3.
  • the status information may include monitoring data of the monitoring unit 16.
  • a monitoring of the state of charge of the energy storage unit 8 and the supply state of the components 4, 6, 10 and 13 of the implanted sensor 2 takes place during the analog / digital conversion and an intermediate storage of the converted data via the monitoring unit 16.
  • the monitoring unit 16 monitors one Charging state of the energy storage unit 8 before, during and after the measurement. During the measurement with the RF field switched off, the voltage of the energy storage unit 8 drops continuously by a few 10 mV.
  • the monitoring unit 16 ensures that the operating voltage of the implanted sensor 2 before, during and after the measurement is within a range specified for the components of the implanted sensor 2.
  • the monitoring data are transferred to the external data-processing device in read-out step. Alternatively or additionally, the microcontroller 10 may perform an evaluation of the monitoring data.
  • the implanted sensor 2 can have an additional voltage stabilization device which measures the voltage of the energy storage unit 8 as the energy storage unit 8. stabilized condenser and thus allows an even more accurate measurement.
  • the control unit 19 controls as a master unit the entire workflow of the transmission device 1.
  • the control unit 19 defines a beginning and a duration of a high-frequency field-free phase within which a measurement and a measurement data conversion takes place in the implanted sensor 2.
  • the microcontroller 10 controls the implanted sensor 2 as its slave.
  • the data communication over the link 21 is additionally secured by a cyclic redundancy check (Cyclic Redundancy Check, CRC) against interference.
  • CRC Cyclic Redundancy Check
  • An operating voltage which is provided by the transmitter unit 13 via the energy storage unit 8 to the other components of the implanted sensor 2 is about 2 V.
  • a current consumption of all circuit parts of the implanted sensor 2 is less than 10 mA.
  • the sequences are synchronized on the one hand in the implanted sensor 2 and on the other hand in the external data processing device 3.
  • the synchronization is also given when the RF field is switched off.
  • a time base for the external data processing device 3 is a quartz oscillator.
  • the time base for the implanted sensor 2 is an RC oscillator or a quartz oscillator.

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  • Health & Medical Sciences (AREA)
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  • Engineering & Computer Science (AREA)
  • Surgery (AREA)
  • Veterinary Medicine (AREA)
  • General Health & Medical Sciences (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Physics & Mathematics (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
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  • Computer Networks & Wireless Communication (AREA)
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  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Arrangements For Transmission Of Measured Signals (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)

Abstract

Dans la transmission de données de détection par un capteur implantable (2) comportant un moyen de capture de données de mesure (4), une unité de stockage d'énergie (8) et une unité d'émission (13) vers un appareil extérieur de traitement de données (3) comportant une unité d'émission/réception (17), un signal de transport d'énergie à haute fréquence est d'abord émis par un dispositif d'alimentation en énergie (18). Au moins une partie de l'énergie contenue dans le signal de transport d'énergie à haute fréquence est stockée dans l'unité de stockage d'énergie (8) du capteur implantable (2). À la fin de l'émission du signal de transport d'énergie à haute fréquence, une mesure est lancée par le moyen de capture de données de mesure (4) du capteur implantable (2). Les données mesurées sont transmises par l'unité d'émission (13) du capteur implantable (2) vers l'unité d'émission/réception (17) de l'appareil extérieur de traitement de données (3). On obtient ainsi un procédé de transmission dans lequel on évite une perturbation due à l'émission HF tout en ayant une construction compacte.
EP12748173.7A 2011-08-01 2012-07-20 Procédé et dispositif pour la transmission de données de détection entre un capteur implantable et un appareil extérieur de traitement des données Withdrawn EP2739202A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102011080192A DE102011080192A1 (de) 2011-08-01 2011-08-01 Verfahren und Vorrichtung zur Übertragung von Sensordaten eines implantierbaren Sensors auf ein externes datenverarbeitendes Gerät
PCT/EP2012/064299 WO2013017440A1 (fr) 2011-08-01 2012-07-20 Procédé et dispositif pour la transmission de données de détection entre un capteur implantable et un appareil extérieur de traitement des données

Publications (1)

Publication Number Publication Date
EP2739202A1 true EP2739202A1 (fr) 2014-06-11

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Application Number Title Priority Date Filing Date
EP12748173.7A Withdrawn EP2739202A1 (fr) 2011-08-01 2012-07-20 Procédé et dispositif pour la transmission de données de détection entre un capteur implantable et un appareil extérieur de traitement des données

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US (2) US9339189B2 (fr)
EP (1) EP2739202A1 (fr)
BR (1) BR112014002371B1 (fr)
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WO (1) WO2013017440A1 (fr)

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US20140210637A1 (en) 2014-07-31
BR112014002371A2 (pt) 2017-02-21
US20160287138A1 (en) 2016-10-06
BR112014002371B1 (pt) 2022-03-03
DE202012013388U1 (de) 2016-09-16
DE102011080192A1 (de) 2013-02-07
WO2013017440A1 (fr) 2013-02-07
US9339189B2 (en) 2016-05-17

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