WO2016134753A1 - Capteur de pression oculaire - Google Patents

Capteur de pression oculaire Download PDF

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Publication number
WO2016134753A1
WO2016134753A1 PCT/EP2015/053823 EP2015053823W WO2016134753A1 WO 2016134753 A1 WO2016134753 A1 WO 2016134753A1 EP 2015053823 W EP2015053823 W EP 2015053823W WO 2016134753 A1 WO2016134753 A1 WO 2016134753A1
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WO
WIPO (PCT)
Prior art keywords
pressure
ocular
pressure sensor
pulse wave
intraocular
Prior art date
Application number
PCT/EP2015/053823
Other languages
English (en)
Inventor
Filippo PIFFARETTI
Achille DONIDA
Original Assignee
Oculox Technology Sagl
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 Oculox Technology Sagl filed Critical Oculox Technology Sagl
Priority to PCT/EP2015/053823 priority Critical patent/WO2016134753A1/fr
Publication of WO2016134753A1 publication Critical patent/WO2016134753A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/16—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for measuring intraocular pressure, e.g. tonometers

Definitions

  • the present application relates to the field of ophthalmological tonometry devices and in particular to ocular pressure sensors and to methods for measuring intraocular pressure.
  • Glaucoma is the leading cause of irreversible blindness worldwide. Its worldwide prevalence exceeds 50 million patients and sounded projections foresee an increase of the glaucoma patients' population up to 100 million by 2040. Poor patient compliance to medication, difficult management and sub-optimal treatment of glaucoma are critical issues that lead to visual impairments and blindness. This entails high health costs and serious social burden.
  • Glaucoma is a pathology which frequently arises as a consequence of an increased intraocular pressure (IOP), above commonly accepted thresholds. Increased IOP is considered to be a leading risk factor for triggering a degenerative process resulting in irreversible damages and progressive loss of the visual field.
  • IOP intraocular pressure
  • aqueous humour i.e. transparent fluids present in the anterior chamber filling the region between the cornea and the lens, and its drainage. Since aqueous humour production and drainage are subject to significant circadian variation, e.g. through hormonal daily rhythm, also the IOP experiences significant variations. Therefore, a precise interpretation of point pressure detections is challenging.
  • Regular IOP monitoring (e.g. daily IOP monitoring service for a week) is a generally accepted medical need to enhance the management of glaucoma. This approach will in fact promote prevention, early detection, allow optimised treatment and act as a compliance check system.
  • the intraocular environment in addition to having an intense metabolic activity, is also characterised to be poorly reactive to foreign bodies and to be a relatively immune- depressed location. This makes it an ideal place to monitor physiologic parameters with long- term implantable devices.
  • Contemporary office-based measurements and devices allow to detect intra ocular pressure and to compare the measured value with a commonly accepted threshold. These measurements are not insufficient to detect daily changes and IOP spikes, nor do they demonstrate the effect of medication or patients' compliance to the prescribed therapy. The detection of the IOP's variation tends to be a more valuable parameter than more standard static measurements.
  • WO2013107677 describes an implant device that measures physical variables in the eye, more particularly the intraocular pressure, comprising a telemetry system which comprises an integrated pressure sensor.
  • the implant device comprises a sensor module having one or a plurality of first fastening devices; an implant module having one or a plurality of second fastening devices; a connecting module by means of which the sensor module is connected to the implant module via the one or the first fastening devices and via the one or the second fastening devices; and a folding axis, along which the implant device can be folded up.
  • state of the art devices take into account the circadian variation only, which has substantially a variation period of 24 hours and amplitudes ranging from some millibars to tens of millibars, where 1 millibar (mbar) is 100 Pascal.
  • the resulting IOP value measured by state of the art devices can thus be used only for detecting whether a certain threshold has been exceeded, with no indication about why and about the actual consequences of this overpressure event/period and whether the measured value should really raise a warning or an alarm for the patient' s health.
  • the health of the corio-retinal vascular network is key for several pathologies of the posterior pole, like diabetic retinopathy, ocular vain occlusion, polypoidal choroidal vasculopathy, age related macular degeneration, retinitis pigmentosa, and so on, and for glaucoma, e.g. normal tension glaucoma.
  • An accurate continuous time and spectral domain analysis of the ocular pulse wave can therefore give important insight which may lead to dramatic change in the management and treatment of these pathologies.
  • the present disclosure is directed, at least in part, to improving or overcoming one or more aspects of the prior art systems.
  • the present disclosure is aimed at providing a system that is capable of measuring intraocular pressure both with respect to the slow varying circadian pressure and with respect to the quickly varying pulse wave pressure.
  • an object of the present disclosure is to provide an implantable sensing device that uses a small amount of components, improving the capabilities of intraocular sensing devices without negatively affecting the size of the sensor device.
  • Another object of the present invention is to provide a sensing device and a system that can be obtained at low costs, partly exploiting and improving on existing technology.
  • the present disclosure describes an ocular pressure sensor for measuring ocular pulse wave, the ocular pressure sensor comprising a pressure sensor for sensing intraocular pressure, means for measuring circadian intraocular pressure and means for measure ocular pulse wave.
  • the present disclosure describes a method for measuring ocular pulse waves with an implanted ocular pressure sensor, comprising the steps of sensing intraocular pressure to determine a measured intraocular pressure value from said sensing; and sensing intraocular pressure to determine ocular pulse wave pressure values based on the measured intraocular pressure value.
  • Fig. 1 is a schematic view of an implantable ocular pressure sensor according to the present disclosure
  • Fig. 2 is a reading system according to the present disclosure
  • Fig. 3 is a block diagram of an ASIC comprised in the ocular pressure sensor of Fig. l;
  • Fig. 4 illustrates a graph of intraocular pressure variation over a period of 24 hours
  • Fig. 5 is a flow diagram for measurement of an ocular pulse wave
  • Fig. 6 is an example of a spectral analysis of an ocular pulse wave.
  • the ocular pressure sensor may be implanted into the eye to measure an ocular pulse wave and thereby the circadian variations of the intraocular pressure.
  • Fig. 1 illustrates an ocular pressure sensor 10.
  • the ocular pressure sensor 10 is implantable in an eye of a patient and, more in detail, ocular pressure sensor 10 may be implantable into the anterior chamber of the eye.
  • Ocular pressure sensor 10 comprises a pressure sensor 12 for sensing intraocular pressure, means for measuring circadian intraocular pressure and means for measuring ocular pulse wave.
  • the ocular pressure sensor 10 comprises an Application Specific Integrated Circuit 14 (ASIC) having embedded sensor readout and telemetry electronics.
  • ASIC Application Specific Integrated Circuit
  • the means for measuring circadian intraocular pressure and means for measuring ocular pulse wave are disposed on the ASIC 14.
  • the pressure sensor 12 may be provided on the ASIC or as a separate module from the ASIC 14.
  • the pressure sensor 12 is a piezoresistive pressure sensor.
  • the piezoresistive pressure sensor may be provided with input-bridge resistances between 5k- 50k ⁇ .
  • the piezoresistive pressure sensor may be provided with sensor sensitivities between 4.5-40 ⁇ /V-mbar.
  • the pressure sensor 12 and the ASIC 14 may be mounted on a substrate 16.
  • the substrate 16 may be flexible.
  • Substrate 16 may be monolithic.
  • the substrate 16 further includes an antenna coil 18.
  • the antenna coil 18 may be connected to the electronics on the ASIC 14.
  • the antenna coil 18 and the associated electronics on the ASIC 14 are devices identified as transponder within the technology known in the art as Radio Frequency Identification (RFID) system. These devices, in addition to the functionalities disclosed in the present document, provide for automatic identification at a distance.
  • RFID Radio Frequency Identification
  • the antenna coil 18 enables RF energy harvesting from a remote power source for supplying the electronics embedded on the ASIC 14 and the pressure sensor 12.
  • Fig. 2 illustrates an exemplary reading system for activating and measuring the intraocular pressure in the eye.
  • a reading unit 20 may serve as a power source.
  • the reading unit 20 emits an electromagnetic field that is captured in the antenna coil 18 to generate a current sufficient to power the implantable ocular pressure sensor 10.
  • the antenna coil 18 enables data transfer to and from a remote reading unit 20.
  • the antenna coil 18 may operate at 13.56 MHz.
  • the reading unit 20 has an antenna 21 for emitting the electromagnetic field and for data transfer.
  • the data collected by the reading unit 20 may be dispatched over to a device 22 for home-based health monitoring.
  • the device 22 may be connected to the reading unit 20 via a network.
  • the device 22 may be connected via Bluetooth 4.0.
  • Devices 22 may be portable.
  • Devices 22 may be handheld devices such as a smartphone or a tablet.
  • the reading unit 20 may be disposed in an eyeglass frame.
  • the ocular pressure sensor 10 may be powered by inductive coupling through the magnetic field generated by the reader unit 20 mounted in the eyeglass frame.
  • the antenna 21 may be disposed in the rim of the eyeglass.
  • the antenna 21 may be disposed in the rim positioned over the eye having the implanted ocular pressure sensor 10.
  • Fig. 3 illustrates a detailed block diagram of the ASIC 14.
  • the ASIC 14 may be implemented in 0.35 ⁇ CMOS technology.
  • the ASIC 14 comprises an analog sensor readout 24, a digital interface 26 and a power management module 28.
  • the analog sensor readout 24 is connected to the pressure sensor 12 through pressure sensor terminals 30.
  • the analog sensor readout 24 is connected to the digital interface 26 through an 8-bit 1.25kb/s analog to digital converter (ADC) 40.
  • ADC analog to digital converter
  • the ocular pressure sensor 10 further comprises a variable amplifying means 32.
  • the variable amplifying means 32 is disposed in the analog sensor readout 24.
  • Variable amplifying means 32 includes two programmable gain stages 34, 36.
  • First gain stage 34 may have a first voltage gain, for instance a gain of 21dB - 40dB.
  • Second gain stage 36 may have a second voltage gain, for instance of 6dB - 60dB.
  • the first and second gain stage 32 are configured to allow an increase in the sensor's analog output voltage so to cover the full dynamic range of the ADC 40.
  • the variable amplifying means 32 is programmable to cover a first pressure range, for measuring intraocular pressure.
  • the first pressure range may vary from 0 mbar to 65 mbar (0 - 6500 Pascal).
  • the variable amplifying means is further programmable to cover a second pressure range, for measuring ocular pulse wave.
  • the second pressure range may vary from 0 mbar to 3.2 mbar (0 - 320 Pascal).
  • the ocular pressure sensor 10 may further comprise a temperature sensor 38 for compensation of thermal drifts, which may occur with piezoresistive pressure sensors.
  • the ocular pressure sensor 10 may further comprise a first compensating means 54 for offsetting atmospheric pressure for measurement of the intraocular pressure.
  • the first compensating means 54 may be a programmable current mirror, e.g. a 10 bit programmable current mirror.
  • the first compensating means 54 is configured to offset the pressure measurement that is produced by the atmospheric pressure.
  • the atmospheric pressure may be measured by an atmospheric pressure sensor located in the reading unit 20.
  • the atmospheric pressure value measured in the reading unit is transferred to the ocular pressure sensor 10 to offset the atmospheric pressure when measuring the intraocular pressure sensed by the pressure sensor 12.
  • the ocular pressure sensor 10 may further comprise a second compensating means 56 for offsetting the atmospheric pressure and the circadian intraocular pressure for measurement of the ocular pulse wave.
  • the second compensating means 56 enables fine compensation during measurement of the ocular pulse wave.
  • the second compensating means 56 may be a programmable current mirror, e.g. a 14-bit programmable current mirror.
  • the first and second compensating means 54, 56 are variable according to the sensibility and resistance of the pressure sensor 12.
  • a chopping technique is used for all the amplifiers inputs.
  • the detailed programmable current mirrors and the sensor analog output signals may be disposed in a 50kHz chopper modulator 62.
  • a correlated double sample block 58 may be provided to cancel any offset and/or noise that are added by the first gain stage 34. Residual high-frequency noise may be filtered out by a cut-off frequency low-pass filter 60, e.g. a 95Hz cut-off frequency Gm-C low-pass filter. The low pass filter 60 may be connected to the correlated double sample block 58.
  • a chopper modulator 62 e.g. a 50kHz chopper modulator, may be provided between the low pass filter 60 and the correlated double sample block 58 to filter residual high-frequency noise.
  • the digital interface 26 is driven by two clock frequencies, for instance running at 800kHz and 13.56MHz respectively.
  • the clock frequencies may be directly extracted from the RFID wave carrier.
  • the digital interface 26 includes an ADC interface 42, an interface to a programmable gain amplifier 44 (PGA) with the variable amplifying means 32, a static signal controller 46 and a sequencer 48, which may be driven at 800kHz.
  • the digital interface 26 includes a communication protocol 50 for data transfer.
  • the communication protocol is preferably a standard communication protocol, e.g. based on ISO 15693, which requires the 13.56MHz clock to encode the data to be transmitted.
  • the logic sequencer (state machine) 48 provides a specific order of operations to perform the amplification routine and the offset routines. The sequence of these routines may enable separation of the intraocular pressure and ocular pulse wave measurements.
  • the digital interface 26 may further include a test mode where the ASIC 14 registers are directly accessible through a serial interface 52, e.g. an I C serial interface.
  • Power management module 28 is connected to the antenna coil 18 through antenna terminals 64. Power management module 28 is connected to the pressure sensor 12 through sensor power terminal 66.
  • Power management module 28 may have a power management circuitry consisting of
  • the power management circuitry further comprises a clock extractor 74, a demodulator 76, a modulator and protection 78, a Power On-Reset (POR) 80 to initialize the ASIC's logic, a frequency divider 82 and a disoverlap phase 84.
  • Fig. 4 illustrates a graph of intraocular pressure variation over a period of 24 hours in a patient.
  • Line A indicates the daily intraocular pressure variation.
  • the intraocular pressure variation is affected by pressure changes caused by cardiac ocular pulse wave as indicated by lines B.
  • Lines B confine a range within which the cardiac ocular pulse wave be disposed.
  • Po ff set indicates the atmospheric pressure.
  • Inset C shows line A and line B over a short period of time.
  • Line B is identified as a wave form in the period of time.
  • Fig. 5 illustrates a method for measuring an ocular pulse wave with the implanted ocular pressure sensor 10.
  • the method comprises the steps of sensing intraocular pressure, measuring intraocular pressure and measuring ocular pulse wave.
  • Information on the intraocular pressure is obtained through the pressure sensor 12.
  • the information is processed in the analog sensor readout 24 embedded in the ASIC 14 to obtain the intraocular pressure.
  • the analog sensor readout 24 then performs further processing to obtain the ocular pulse wave.
  • the method may be implemented by the logic sequencer 48.
  • the method is initiated by selecting the circadian intraocular pressure measurement mode for ocular pressure sensor 10 and by measuring the actual atmospheric pressure.
  • the actual atmospheric pressure may be measured at step 86.
  • the atmospheric pressure is sensed by a pressure sensor disposed in the reading unit.
  • the obtained atmospheric pressure value thanks to a previous system calibration, is processed and used to set the registers of first compensation offset 54.
  • the atmospheric pressure information to set the first compensation offset and measure the circadian intraocular pressure is obtained at the beginning of every measurement.
  • the pressure information is obtained from the pressure sensor 12.
  • the prevailing intraocular pressure is then processed by the variable amplifying means 32.
  • the variable amplifier means 32 is set to cover a first pressure range, e.g. from 0 mbar to 65 mbar (0 - 6500 Pascal), for measuring the circadian intraocular pressure in step 90.
  • the circadian intraocular pressure is obtained as the average value of three measurements with a 0.22 mbar (22 Pascal) accuracy.
  • the mean circadian intraocular pressure value is then stored in step 92.
  • the intraocular pressure value may be stored in the reading unit 20.
  • the intraocular pressure value may be sent to device 22.
  • the pressure information is obtained from the pressure sensor 12.
  • the pressure information is then processed by the second compensating means 56.
  • the pressure information is processed in a step of offsetting atmospheric pressure and the measured intraocular pressure from the sensed intraocular pressure in step 94.
  • the pressure information used to measure the circadian intraocular pressure is used to measure the ocular pressure wave (through offset cancellation).
  • the pressure information used to measure the ocular pulse wave may be obtained in a separate time interval from the pressure information used to measure the intraocular pressure.
  • Pressure information for measurement of the ocular pulse wave may be obtained over a period of some seconds, e.g. over an interval of 5 seconds, operating at 1.25 kbps and with an accuracy of 36 ⁇ bar.
  • Updated pressure information may be obtained at regular interval, for instance at every 15 minutes, and may continue over a period of 24 hours to 192 hours or more, based on requirements.
  • variable amplifying means 32 Pressure information processed by a step of offsetting atmospheric pressure and the measured intraocular pressure is then further processed by the variable amplifying means 32.
  • the variable amplifying means 32 is thus set to cover a second pressure range for measuring the ocular pressure wave in step 96.
  • the second pressure range has a narrower amplitude compared to the first pressure range and is preferably set from 0 mbar to 3.2 mbar (0 - 320 Pascal).
  • steps 98 - 100 fine compensation of the measured ocular wave is performed.
  • Step 98 initiates the fine compensation step wherein the sensor's analog output signal, that is already compensated, is then amplified to precisely fit the ACD dynamic range (0 ⁇ ocular pulse wave ⁇ ADCps).
  • step 100 if the value of the measured ocular pressure wave is greater than zero and less than the value of the ADC 40 at full scale, then the value is stored at step 102.
  • step 100 if the value of the measured ocular pressure wave is less than or equal to zero or greater than or equal to the value of the ADC 40 at full scale, then step 98 is reinitiated.
  • the system (ocular pressure sensor 10 and reading unit 20) are well characterized, calibrated and functional.
  • the precise response curve of the pressure sensor 12 is known for the system to be characterized and calibrated.
  • the pressure sensor 12 analog output value can be inferred as function of a defined environmental pressure for any combination of values of the first and second compensation means 54, 56 and the variable amplifying means 32.
  • the atmospheric pressure as function of the pressure sensor 12 analog output value can be inferred for any combination of values of the first and second compensation means 54, 56 and the variable amplifying means 32.
  • the pressure measuring procedure starts with the reading unit 20 measuring the atmospheric pressure and stores its digital value.
  • the stored atmospheric pressure value is analysed by the reading unit 20 (pressure sensor response curve 12) to find the analog voltage to be transferred to the ocular pressure sensor 10 and correctly set the offset values through the first compensation means 54.
  • the gains to be transferred and set to the first and second gain stages 34, 36 are pre-determined during calibration.
  • the expected pressure range is set for a range of 7 - 65 mbar (700 - 6500 Pascal).
  • the offset values (atmospheric pressure) and the gain are transferred through RFID from the reading unit 20 to the ocular pressure sensor 10.
  • the PGA digital interface registers 44 are consequently set. Therefore the pressure measured with the pressure sensor 12 will be compensated from the atmospheric pressure and falls within the dynamic range of the ADC 40.
  • the intraocular pressure measured is transferred through RFID to the reading unit 20 and corresponds to the circadian intraocular pressure.
  • the average over 3 consecutive measurements (procedure time 50 ms) is carried out.
  • the result corresponds to an approximation of the mean circadian intraocular pressure.
  • the result is stored in the reading unit 20 together with a precise timestamp.
  • the stored mean circadian intraocular pressure value is analysed by the reading unit 20 (pressure sensor response curve 12) to find the analog voltage to be transferred to the ocular pressure sensor 10 and correctly set the offset values through the second compensation means 54.
  • the approximate gains to be transferred and set to the first and second gain stages 34, 36 are pre-determined during calibration.
  • Expected pressure is set for a range of 0 - 3.2 mbar (0 - 320 Pascal).
  • the offset values, (atmospheric and circadian intraocular pressure) and the gain are transferred through RFID from the reading unit 20 to the ocular pressure sensor 10.
  • the PGA digital interface registers 44 are consequently set. Therefore the pressure measured with the sensor 12 will be compensated from the atmospheric pressure and circadian intraocular pressure and falls within the dynamic range of the ADC 40. Through the offset compensation the pressure sensor 12 analog output signal moves about the centre of the dynamic range of the ADC 40.
  • a fine compensation procedure then initiates.
  • the logic sequencer 48 automatically fine tunes the second gain stage 36 values so as to optimise the ADC 40 signal conversion.
  • the gain of the second gain stage 36 is varied to have a peak to peak analog signal maximizing the dynamic range of the ADC.
  • the digital signal coming out the ADC ranges from 0 to 255 (8-bit ADC full scale).
  • the final PGA gains and offsets are transferred and stored in the reading unit 20. These values are used to infer pressure values from the stored digital data.
  • the data measured by the ocular pressure sensor 10 are continuously transferred (1.25kbps) and stored in the reading unit 20. This procedure (measurement campaign) lasts 5 seconds. The measurements have a quantization precision of 36 ⁇ bar. Each stored data is accompanied by precise timestamp data to be able to reconstruct the signal.
  • the combination of the pressure sensor 12 characterisation-calibration, knowledge of the offset and gain used, stored digital data and data timestamp enables data analysis.
  • This disclosure describes an ocular pressure sensor 10 to measure variations in the circadian intraocular pressure and the ocular pulse wave.
  • the ocular pressure sensor 10 simultaneously measures the circadian intraocular pressure and the ocular pulse wave.
  • the ocular pressure sensor 10 provides for automatic calibration, compensation of ambient pressure and telemetric data transfer.
  • Contemporary office-based measurements are not sufficient to discover daily changes and intraocular pressure spikes, nor do the measurements demonstrate the effect of medication or patients' compliance to the prescribed therapy.
  • the detection of the intraocular pressure variation is already a more accurate parameter than the standard static measurement.
  • spectral analysis of the cardiac ocular pulse wave up to the third harmonic of the cardiac rate (+1.6mbar, i.e. 160 Pascal, at 2-3Hz around the circadian intra ocular pressure), may further provide information on the health of the retinal vasculature. This information may be used to diagnose ocular pathologies such as glaucoma and other diseases.

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  • Life Sciences & Earth Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
  • Eye Examination Apparatus (AREA)
  • Prostheses (AREA)

Abstract

La présente invention concerne un capteur de pression oculaire (10) destiné à mesurer directement l'onde de pression oculaire, le capteur de pression oculaire (10) comprenant un capteur de pression (12) pour détecter la pression intraoculaire ; un moyen de mesure des variations de pression intraoculaire circadiennes ; et un moyen de mesure de l'onde de pression oculaire.
PCT/EP2015/053823 2015-02-24 2015-02-24 Capteur de pression oculaire WO2016134753A1 (fr)

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PCT/EP2015/053823 WO2016134753A1 (fr) 2015-02-24 2015-02-24 Capteur de pression oculaire

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PCT/EP2015/053823 WO2016134753A1 (fr) 2015-02-24 2015-02-24 Capteur de pression oculaire

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WO2016134753A1 true WO2016134753A1 (fr) 2016-09-01

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2689733C1 (ru) * 2018-10-09 2019-05-28 Олег Леонидович Головков Способ измерения внутриглазного давления и устройство для его осуществления

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2003088829A2 (fr) * 2002-04-19 2003-10-30 The Queen's University Of Belfast Appareil de mesure de l'impedance vasculaire
JP2004065298A (ja) * 2002-08-01 2004-03-04 Nidek Co Ltd 非接触式眼圧計
WO2012136431A1 (fr) * 2011-04-07 2012-10-11 Sensimed Sa Dispositif et procédé de détection de maladies ophtalmiques et/ou cérébrales

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2003088829A2 (fr) * 2002-04-19 2003-10-30 The Queen's University Of Belfast Appareil de mesure de l'impedance vasculaire
JP2004065298A (ja) * 2002-08-01 2004-03-04 Nidek Co Ltd 非接触式眼圧計
WO2012136431A1 (fr) * 2011-04-07 2012-10-11 Sensimed Sa Dispositif et procédé de détection de maladies ophtalmiques et/ou cérébrales

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2689733C1 (ru) * 2018-10-09 2019-05-28 Олег Леонидович Головков Способ измерения внутриглазного давления и устройство для его осуществления

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