WO2007083991A1 - Appareil et procede d'analyse optique - Google Patents

Appareil et procede d'analyse optique Download PDF

Info

Publication number
WO2007083991A1
WO2007083991A1 PCT/NL2006/000029 NL2006000029W WO2007083991A1 WO 2007083991 A1 WO2007083991 A1 WO 2007083991A1 NL 2006000029 W NL2006000029 W NL 2006000029W WO 2007083991 A1 WO2007083991 A1 WO 2007083991A1
Authority
WO
WIPO (PCT)
Prior art keywords
probe
information
base unit
light
optical fibre
Prior art date
Application number
PCT/NL2006/000029
Other languages
English (en)
Inventor
Henricus Josephus Cornelus Maria Sterenborg
Arjen Amelink
Johannes Antonius Maria Kuijpers
Original Assignee
Erasmus University Medical Center Rotterdam
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 Erasmus University Medical Center Rotterdam filed Critical Erasmus University Medical Center Rotterdam
Priority to PCT/NL2006/000029 priority Critical patent/WO2007083991A1/fr
Publication of WO2007083991A1 publication Critical patent/WO2007083991A1/fr

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4738—Diffuse reflection, e.g. also for testing fluids, fibrous materials
    • G01N21/474—Details of optical heads therefor, e.g. using optical fibres
    • 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
    • A61B5/1495—Calibrating or testing of in-vivo probes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4785—Standardising light scatter apparatus; Standards therefor
    • 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
    • A61B2560/0223—Operational features of calibration, e.g. protocols for calibrating sensors
    • A61B2560/0228—Operational features of calibration, e.g. protocols for calibrating sensors using calibration standards
    • A61B2560/0233—Optical standards
    • 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
    • A61B2560/0266—Operational features for monitoring or limiting apparatus function
    • A61B2560/0271—Operational features for monitoring or limiting apparatus function using a remote monitoring unit
    • 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
    • A61B2562/085—Sensors provided with means for identification, e.g. barcodes or memory chips combined with means for recording calibration data
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2201/00—Features of devices classified in G01N21/00
    • G01N2201/12—Circuits of general importance; Signal processing
    • G01N2201/121—Correction signals

Definitions

  • the invention relates to an optical analysis apparatus with an exchangeable probe that contains an optical fibre.
  • PCT patent application WO2005029051 discloses a device with a probe that contains two optical fibres. This device is used to measure a physical feature, such as a concentration of a substance (e.g. oxygenated blood) at a location near the distal end of the probe.
  • a substance e.g. oxygenated blood
  • a similar device is describe in an article published in Applied Optics VoI 43 No 15 pages 3048-3054, titled "Measurement of the local optical properties of turbid media by differential path-length spectroscopy" by. A. Amelink and H. J. CM. Sterenborg.
  • a measurement set-up is used wherein the probe is attached to a base unit that includes a light source, detectors and computation circuitry.
  • the probe is included in the working channel of a clinical endoscope or biopsy device.
  • the base unit feeds light to the proximal end of the probe to the distal end through a first fibre.
  • the first fibre delivers the light to sample tissue or fluid near the distal end. Reflected or scattered light is collected at the distal end and led back through the first fibre and a second fibre in the probe, from which it is delivered at the proximal end.
  • the base unit measures light properties of the light received from the first and second fibre and computes material properties of the sample tissue or fluid from the light properties.
  • the base unit uses a mathematical formula that relates a wavelength dependent backscatter coefficient to wavelength dependent intensity of light from the second fibre, intensity of light fed to the first fibre, intensity of light that the measurement set-up measures from a highly reflective reference medium and a not or hardly reflective reference medium and a liquid that has an index of refraction that is approximately equal to that of the tissue that must be investigated.
  • This type of measurement requires accurate calibration of the properties of the optical fibres in the probe. Unfortunately, these properties may vary from probe to probe.
  • a first and second calibration measurement are used wherein the probe is applied to a highly reflective reference medium and a not or hardly reflective reference medium respectively to measure the intensity. Such a calibration makes measurements cumbersome.
  • probes are used only for one patient and subsequently discarded. Manufacturers supply sterilized probes, which are attached to the base unit for performing tests on a single patient. The calibration of the measurement set-up with reference media when a new probe is attached can compromise sterility.
  • probe as used herein is not limited to probes for measurement.
  • a treatment probe may be used, for supplying light to tissue through an optical fibre in the probe.
  • This type of probe may also require calibration, for example to set the power level of light supplied to the probe so that a desired power density is realized in the tissue. Calibration for this purpose may also compromise sterility of the probe.
  • a probe has been reused.
  • used probes are typically not sterile any more.
  • a base unit is able to operate in different modes for different probes, for example to perform different forms of analysis or treatment for different types of tissue. If the wrong mode of operation is used for a probe for a certain type of analysis or treatment undesirable results may occur.
  • An apparatus is provided.
  • a base unit and an exchangeable probe are used that can be attached to the base unit and detached from it using connection part.
  • the probe contains an information- providing element and at least one optical fibre.
  • the base unit comprises a reading device arranged to read probe information from the information- providing element.
  • the probe information is read automatically while the probe is attached to the base unit.
  • the base unit contains a processor circuit which controls operation of the base unit dependent on the probe information.
  • the probe information is used to correct light measurements results for light received from the probe, for example to compensate for transmission and/or reflection properties of the probe.
  • the probe information is used to control properties of light supplied from the base unit to the probe, for example to compensate for transmission and/or reflection properties of the probe.
  • the probe information is used to enable or disable use of the probe, for example dependent on whether the probe has been used before.
  • Information whether the probe has been used before may be stored in the probe by the base unit, when a writable information providing element is used.
  • an identifier in the probe information may be used to retrieve and update this type of information about use of the specific probe in a database, the database being used to select between enabling and disabling use of the probe. In this way reuse of probes that are not sterile due to previous use can be disabled.
  • the probe information provides for correction information about transmission and/or reflection by the optical fibre.
  • the correction information may be stored in the probe or in a database that is accessible to the base unit, wherein the correction information for the probe is linked to an identifier that is stored in the information-providing element.
  • the probe information identifies an internal reflection parameter for the optical fibre, for use to remove an effect of internal reflection from a detection result.
  • the probe contains a first and second optical fibre, for supplying light to a sample medium through the first optical fibre and for receiving back light scattered by the sample medium through both the first and second fibre. In this embodiment a measurement of intensity of light from the second fibre is subtracted from a measurement of intensity of light from the first fibre. Thus, information about the sample medium near the distal face of the fibre is obtained.
  • the correction information comprises identifies a ratio between light collection efficiencies of the first and second optical fibre of the probe.
  • the measurement is corrected for the ratio between the light collection efficiencies identified by the probe information.
  • a correction is made for internal reflections in the first optical fibre, using probe information identified by the information-providing element.
  • Figure 1 shows a measurement set up
  • Figure 2 shows part of a base unit
  • Figure 3 shows a networked set up
  • FIG. 1 shows a measurement set-up.
  • the measurement set up contains a base-unit 10 and a probe 12 in the working channel 14 of a clinical endoscope or biopsy device.
  • Base unit 10 comprises a light source 100, a detection arrangement 102, a first connector 104, a reading device 106 and a processing circuit 108.
  • Light source 100 is arranged to supply light to first connector 104.
  • Detection arrangement 102 is arranged to receive light from first connector 104 and to generate measurement signals that are indicative of the properties of the received light.
  • Processing circuit 108 has inputs coupled to the detection arrangement 102 and reading device 106.
  • Probe 12 contains a first optical fibre 120, a second optical fibre 122, an information-providing element 124 and a second connector 126.
  • Second connector 126 is shown coupled to first connector 104.
  • a detachable form of coupling is used, for example a screw-on or click-on coupling.
  • First optical fibre 120, second optical fibre 122, and information-providing element 124 are coupled to second connector 126 and arranged so that light from light source 110 is fed to first optical fibre 120, light from second optical fibre 122 is fed to detection arrangement 102 and reading device 106 is able to read data from information-providing element 124.
  • first and/or second optical fibre 120, 122 may be arranged in parallel with first and/or second optical fibre 120, 122.
  • the details of the fibres are not relevant for understanding the present invention. Such details can be found in
  • first optical fibre 120 may have a skewed distal surface to reduce internal reflections.
  • a flash memory is used with terminals coupled to second connector 126.
  • connectors 104, 126 may be provided with mated electrodes and reading device 106 is a memory interface circuit.
  • Processing circuit 108 may be arranged to address locations in the flash memory using reading device 106 as interface, or reading device 106 may be arranged to address standard locations.
  • a PROM EPROM or any other type of non- volatile memory may be used.
  • a remotely readable circuit (e.g. an RF readable circuit using known RFID transponder technology) may be used as an information-providing element 124.
  • connectors 104, 126 do not need mating electrodes and reading device 106 is a remote reading device located so that it can transmit signals to the remotely readable circuit and receive responses from the remotely readable circuit.
  • an optically readable pattern such as a bar code may be used as an information-providing element 124.
  • reading device 106 may be a scanner, a camera or the like, for optically reading the optically readable pattern.
  • information-providing element 124 and connectors 104, 126 are arranged so that, when the connectors are mated, the reading device is capable of "seeing" information-providing element 124.
  • Figure 2 schematically shows connection details of an embodiment.
  • detection arrangement 102 comprises a first, second and third detector 20, 22, 24.
  • First connector 104 comprises a first and second fibre interface 26, 28, for first and second fibre 120, 122 respectively.
  • base unit 10 comprises a calibration interface 29.
  • a reflector box 290 is coupled to calibration interface 29.
  • First and second source interface fibres 26a, 29a couple light source 100 to the fibre faces in first fibre interface 26 and to calibration interface 29 respectively.
  • First detector 20 is coupled to a fibre face in first interface 26 via a first measurement interface fibre 26b.
  • Second detector 22 is coupled to a fibre face in second fibre interface 28 for second fibre 122 via a second measurement interface fibre 28a.
  • Third detector 24 is coupled to calibration interface 29 via a calibration interface fibre 29b.
  • First and second optical fibre 120, 122 and interface fibres 26a, b, 28a have fibre faces (preferably substantially perpendicular to the length of the fibres) facing each other.
  • the fibres have been shown as lines, but it will be understood that the fibres have a finite diameter.
  • the faces of the interface fibres 26a, b on one hand and first optical fibre 120 face each other in first interface 26 so that light from first source interface fibre 26a is transmitted to first optical fibre 120 and light from first optical fibre 120 is transmitted to measurement fibre 26b (and to first source interface fibre 26a, but this does not matter).
  • first and second optical fibre 120, 122 have a different diameter compared with interface fibres 26a, b, 28a, 29a,b. This has the advantage that small relative position variations that may occur due to the exchangeable connection of probe 12 to base unit 10 have little or no effect on coupling.
  • first and second optical fibre 120, 122 have a larger diameter than interface fibres 26a, b, 28a, 29a,b.
  • first detector 20 measures light intensity of light returning from first interface 26 as a function of wavelength and passes measurement results to processing circuit 108.
  • Second detector 22 measures intensity of light returning from second interface 28 as a function of wavelength.
  • Third detector 24 measures the intensity of light reflected by reflector box 290 as a function of wavelength.
  • sample measurement is performed, during which first sample measurement light source 100 is activated and light from light source 100 is passed to first optical fibre 120 via first source interface fibre 26a.
  • First optical fibre 120 passes some of this light to the sample medium at the distal end of probe 12.
  • the sample medium scatters back the light, into both first and second optical fibre 120, 122.
  • the distal ends of the first and second optical fibre 120, 122 are located near each other sot that generally the scattered light collected by first and second optical fibre 120 comes from a same volume in the medium, except that first optical fibre also collects scattered light from a volume immediately in front of the distal end of the first optical fibre 120, which volume is not visible from the second optical fibre 122.
  • the first and second optical fibre 120, 122 feed back the collected light to first and second detector 20, 22, which measure the intensity of the scattered light as a function of wavelength.
  • a result derived from the second detector 22 detectors is subtracted from a result derived from the first detector 20, so that the difference represents mainly the intensity of scattered light from a volume immediately in front of the distal end of the first optical fibre 120. For reasons set out in WO2005029051 this is a diagnostically useful signal.
  • first optical fibre 120 A number of corrections are desirable to make the result more reliable.
  • the probe calibration measurements are performed at a specialized calibration site, in a form of serial production for a batch of different probes
  • the probes 12 are sterilized after calibration, packaged and delivered to users, for connection to a base unit 10.
  • the probe calibration measurements may be performed shortly after manufacture of probe 12.
  • the first probe calibration measurement is performed by coupling the probe under calibration to a calibration device with a structure similar to base unit 10.
  • a calibration device with a structure similar to base unit 10.
  • the distal end of the probe under calibration is placed in a reference medium (e.g. water), reflector box 290 is placed on calibration interface and light is supplied from the calibration device to the probe.
  • the detection signals representing the intensity of reflected light at the first detector 20 in the calibration device is then measured. Calibration results derived from these detection signals are written to the information-providing element 124 of the probe under calibration.
  • processing circuit 108 causes these calibration results to be read from information-providing element 124 and subtracted from measurement results derived from first detector 20 (or from a difference between results from first and second detector 20, 22). Thus a correction for internal reflections is realized.
  • Figure 3 shows an arrangement of an alternative embodiment, wherein the base unit 10 and a calibration device 30 are coupled to a database server 34 via a network 32 (probe not shown).
  • information- providing element 124 stores an identifier that uniquely identifies the probe 12.
  • Calibration device 30 writes results of the calibration with a link to the identifier to a database in database server 34.
  • processing circuit 108 causes the identifier to be read from information-providing element 124 and use the identifier to retrieve the calibration results from the database. In this case there is no need to write calibration results to information- providing element 124, so that a read only information-providing element 124 may be used.
  • the calibration result of the probe calibration measurement which is subtracted from the output signal of first detector 20 is simply the output signal of first detector 20 of the calibration device.
  • the dependence on the intensity of the light source is removed by measuring the wavelength dependent intensity of the light sources of base unit 10 and the calibration device and modifying the correction to account for differences between the intensities.
  • the results during normal use may be corrected by adding the known response from the reference medium.
  • a reference medium independent measurement can be obtained.
  • calibration data for performing other corrections may be written alone, or combination with the calibration result for correcting for internal reflection.
  • data is provided in order to correct for difference between the light collection efficiency of the first and second optical fibre.
  • the probe under measurement is coupled to a calibration device that may be similar in structure to base unit 10 and light from a light source is supplied from outside the probe under measurement to the distal end of first and second optical fibre 120, 122.
  • a setup is used wherein light supplied to both has the same wavelength dependent intensity, which can be easily realized because the distal ends are located closely together.
  • the calibration information may include for example a ratio between detected intensities at the first and second detector in the calibration device.
  • the intensities obtained from first and second detector 20, 22 of base unit 10 are corrected according to the calibration information, for example by scaling one intensity according to the ratio.
  • a correction for relative sensitivity differences between at least the first detector 20 and second detector 22 in the base unit 10 and the calibration device is provided.
  • light from a light source is supplied to the interfaces 26, 28 at first connector 104 of the calibration device.
  • the resulting wavelength detection signals from first and second detector 20, 22 are recorded. From these detection signals relative correction factors for the relative sensitivity of the first detector 20 and second detector 22 of the calibration device are determined as a function of wavelength. The calibration information obtained for the probe is then corrected for these relative correction factors. A similar procedure is followed for base unit 10, to obtain relative correction factors as a function of wavelength for the first detector 20 and the second detector 22 in base unit 10. These relative correction factors are used to perform a relative correction of the results from the detectors obtained when probe 12 is used. It is emphasized that this embodiment is optional: such a correction can be avoided if accurately matched detectors are used. Also various other forms of (relative) calibration of the detectors may be used.
  • a calibration interface 29 and a reflector box 290 are used to correct for fluctuations of the intensity of light source 100.
  • a measurement form third detector 24 is obtained, of the intensity as a function of wavelength of light from light source 100 that is reflected by reflector box 290.
  • a diffuse reflector with a wavelength independent reflection coefficient is used but this is not necessary.
  • a fibre running from light source 100 to third detector 24 may be used instead of a configuration with a reflector box.
  • Intensity measurements from first detector 20 and second detector 22 are then normalized as a function of wavelength according to the intensity measurements from third detector 24. This may be applied to measurements in the calibration device and the measurements in base unit 10.
  • the effect of intensity fluctuations, including wavelength dependent relative fluctuations is eliminated.
  • calibration interface 29 and reflector box 290 may be omitted from base unit. Also, as mentioned, other arrangements for performing reference measurement on light from light source 100 may be used.
  • the relative sensitivity of first, second and third detector 20, 22, 24 of the base unit or calibration device is calibrated using a further measurement which is performed when no probe is attached to the base unit or calibration device and reflector box 290 is temporarily.
  • reference light from outside the device is applied to interfaces 26, 28 and calibration interface 29.
  • the resulting intensity measurements as a function of wavelength from detectors 20, 22, 24 are recorded.
  • a ratio between the results from first and second detector 20, 22 on one hand and third detector 24 on the other hand is used to correct other measurements from the first and second detectors, in conjunction with the normalization that is used to eliminate the effect of fluctuations in the light source.
  • a calibration normalized against the reference light is realized. It should be noted that such a normalized calibration is optional. Relative measurements may suffice, or other forms of calibration of the detectors may be used.
  • detectors 20, 22, 24 are arranged so that their output signals as a function of wavelength are each proportional to the received intensity. In this case no further correction is needed.
  • an arrangement is used wherein detectors 20, 22, 24 output signals proportional to an offset plus intensity from first and second optical fibre 120, 122.
  • the offset may be due for example to spurious light in base unit 10, or it may be inherent in the detectors.
  • a first and second sub-measurements are used for each measurement, a first measurement wherein processing circuit 108 has switched light source 100 on and a second measurement wherein processing circuit 108 has switched light source 100 off.
  • processing circuit 108 has been shown in a box labelled base unit 10, it should be appreciated that this processing circuit 108 may be a device on its own, such as a PC (personal computer) or any other computer, coupled to the detector arrangement and the reading device via any suitable interface (e.g. a USB interface or a PCI bus). Alternatively processing circuit 108 may be integrated in base unit, for example in the form of a firmware programmed microcomputer or a signal processor.
  • information-providing element 124 and reading device 106 is not limited to such measurements.
  • these elements may also be used for a probe with a single fibre, to represent transmission properties and/or internal reflection properties of this fibre. Similarly these elements may be used for a probe with more fibres.
  • information-providing element 124 is used to represent both calibration information to correct for internal reflections (e.g. at the distal end) from first optical fibre 120 and relative transmission efficiency through first and second optical fibre 120, 122 as a function of wavelength of the transmitted and reflected light.
  • wavelength independent information about internal reflection and relative transmission efficiency may be represented. This may be done for example when these parameters do not vary over the wavelength range of interest, or if the wavelength dependence can be reconstructed by processing circuit 108 by means of a mathematical model.
  • calibration information for only relative transmission efficiency or for only internal reflection is provided. This may be done for example if no correction for one of these properties is needed, or if the correction can be computed by processing circuit 108 by means of a mathematical model.
  • information-providing element 124 is located so that reading device 106 is able to read information from information-providing element 124 when probe 12 is attached to the base unit 10 by the connectors.
  • the information-providing element 124 may be provided so that an additional reading action from the user is needed, for example holding a part of probe 12 near reading device 106.
  • base unit 10 is provided with a detector (e.g.
  • processing circuit 108 is configured to output a query signal in response to detection, for causing the user to perform the additional reading action.
  • the corrections using the calibration information for the probe and/or calibration data for the base unit are performed when the signals from first and second detectors 20, 22 are received.
  • some or all of the calibration measurements may be performed subsequently, the correction being performed only after all required calibration measurements have been made.
  • probe calibrations are performed subsequently an identifier from information-providing element 124 is used to ensure that the normal operation measurements and the probe calibration measurements for the same probe are combined.
  • the apparatus may be used to control intensity of light supplied to an optical fibre 120, to enable or disable the apparatus and/or to select a mode of operation.
  • processing circuit 108 is configured to control the intensity of light supplied to first optical fibre 120, for example by controlling energy supplied to light source 100, or by controlling an optional attenuator (not shown) between light source 100 and first optical fibre 120.
  • the intensity as a function of wavelength is controlled.
  • processing circuit 108 is configured to control the intensity dependent on information obtained using information-providing element 124 (e.g. directly, or by means of information from a database selected using information from information-providing element 124).
  • processing circuit 108 is configured to control the intensity so that a predetermined nominal intensity will be received back from the sample at first connector. Thus, less correction of the measurements is needed.
  • processing circuit 108 is configured to control the intensity so that a desired nominal intensity will be delivered at the distal end of the probe, by compensating the intensity at the connector for measured transmission and/or reflection losses of the first optical fibre 120. This may be useful to control treatment of tissue at the distal end of first optical fibre 120. It may be noted that in this case second optical fibre may not be needed in this case.
  • the required calibration data may be obtained for example by measuring intensity delivered at the distal end via the probe when the probe is in a calibration set-up and subsequently sterilizing the probe. In this case a result of the measurements is written into information providing element 124 or in a database, for use during normal operation.
  • the delivered intensity at the connector is measured with third detector 24 and the intensity is controlled so that this measurement corresponds to a level that will result in a desired output intensity at the distal end for the probe that is used (taking account of losses that are particular for the probe). If necessary processing circuit 108 can compensate for the sensitivity of its third detector 24 and/or the response behavior of its light source 100.
  • the delivered intensity may be measured with second optical fibre 122 and the intensity is controlled so that this measurement corresponds to a desired output intensity at the distal end for the probe that is used, after correction for the effect on the measurement due to losses that are particular to the probe.
  • processing circuit 108 is configured to respond dependent on information about previous use of the probe.
  • processing circuit 108 is configured to maintain this information, for example to write this information to information providing element 124 when the probe is used, or to write to a database using an identifier obtained from information providing element 124.
  • a writable information providing element 124 is used for this purpose, containing a non- volatile memory for example.
  • processing circuit 108 detects previous use, it preferably causes base unit 10 to generate an alarm signal and disables operation.
  • the alarm signal my be an audio signal for example, or a visual signal, or the absence of an approval signal from base unit 10.
  • processing circuit 108 disables operation using the probe in this case, operation being enabled only if the information indicates that the probe has not been used before.
  • processing circuit 108 is configured to select between different modes of operation dependent on a type of the probe.
  • different types of probe may be provided to cooperate with base unit 10 in different ways, for example to investigate different types of tissue or to apply different types of light treatment.
  • processing circuit 108 implements the different ways of cooperation by operating in different modes (e.g. applying mode dependent light intensity, or performing mode dependent computations on detected light intensity to produce a measurement result).
  • processing circuit 108 is configured to read information about the type of the probe from information providing element 124, and to switch to a selected one of the modes dependent on the information about the type.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Pathology (AREA)
  • Chemical & Material Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Optics & Photonics (AREA)
  • Biophysics (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)

Abstract

L'invention concerne un appareil d'analyse optique doté d'une sonde interchangeable contenant une fibre optique permettant d'effectuer des mesures ou d'administrer un traitement. L'appareil comprend une unité de base contenant une source de lumière et/ou un détecteur de lumière servant à émettre de la lumière en direction de la fibre optique et/ou à détecter la lumière émanant de la fibre optique. La sonde contient un élément générant des informations lisibles par ordinateur. L'élément générateur d'informations incorporé dans la sonde transmet préalablement des informations relatives à la sonde à l'unité de base pour en commander le fonctionnement. Dans un mode de réalisation, les informations relatives à la sonde comprennent (ou se rapportent à) des résultats de mesures d'étalonnage de la sonde et la lumière émise en direction de la sonde et/ou les signaux traités reçus de la sonde sont corrigés en fonction des résultats des mesures obtenues à partir de l'élément générateur d'informations. Dans d'autres modes de réalisation, les informations sont utilisées pour éviter la réutilisation d'une sonde qui a servi dans une procédure susceptible d'en compromettre la stérilité.
PCT/NL2006/000029 2006-01-19 2006-01-19 Appareil et procede d'analyse optique WO2007083991A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/NL2006/000029 WO2007083991A1 (fr) 2006-01-19 2006-01-19 Appareil et procede d'analyse optique

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/NL2006/000029 WO2007083991A1 (fr) 2006-01-19 2006-01-19 Appareil et procede d'analyse optique

Publications (1)

Publication Number Publication Date
WO2007083991A1 true WO2007083991A1 (fr) 2007-07-26

Family

ID=36939124

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/NL2006/000029 WO2007083991A1 (fr) 2006-01-19 2006-01-19 Appareil et procede d'analyse optique

Country Status (1)

Country Link
WO (1) WO2007083991A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010143119A3 (fr) * 2009-06-10 2011-04-07 Koninklijke Philips Electronics N.V. Algorithme pour console d'aiguille photonique
CN103082998A (zh) * 2013-01-29 2013-05-08 无锡微奥科技有限公司 一种手持mems光学扫描装置
WO2014014560A1 (fr) * 2012-07-20 2014-01-23 Lightlab Imaging, Inc. Codeurs de données pour dispositifs médicaux et procédés associés
CN117179692A (zh) * 2023-11-08 2023-12-08 苏州术客高鑫科技有限公司 一种可装载光纤导管的宫颈筛查手柄

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5769791A (en) * 1992-09-14 1998-06-23 Sextant Medical Corporation Tissue interrogating device and methods
US20040039274A1 (en) * 2002-04-09 2004-02-26 Spectros Corporation Spectroscopy illuminator with improved delivery efficiency for high optical density and reduced thermal load
US20040231772A1 (en) * 2002-11-12 2004-11-25 Leonard Todd E. Intelligent medical device barrier

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5769791A (en) * 1992-09-14 1998-06-23 Sextant Medical Corporation Tissue interrogating device and methods
US20040039274A1 (en) * 2002-04-09 2004-02-26 Spectros Corporation Spectroscopy illuminator with improved delivery efficiency for high optical density and reduced thermal load
US20040231772A1 (en) * 2002-11-12 2004-11-25 Leonard Todd E. Intelligent medical device barrier

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010143119A3 (fr) * 2009-06-10 2011-04-07 Koninklijke Philips Electronics N.V. Algorithme pour console d'aiguille photonique
US8812080B2 (en) 2009-06-10 2014-08-19 Koninklijke Philips N.V. Algorithm for photonic needle console
RU2544465C2 (ru) * 2009-06-10 2015-03-20 Конинклейке Филипс Электроникс Н.В. Алгоритм для консоли фотонной иглы
WO2014014560A1 (fr) * 2012-07-20 2014-01-23 Lightlab Imaging, Inc. Codeurs de données pour dispositifs médicaux et procédés associés
CN103082998A (zh) * 2013-01-29 2013-05-08 无锡微奥科技有限公司 一种手持mems光学扫描装置
CN103082998B (zh) * 2013-01-29 2015-12-16 无锡微奥科技有限公司 一种手持mems光学扫描装置
CN117179692A (zh) * 2023-11-08 2023-12-08 苏州术客高鑫科技有限公司 一种可装载光纤导管的宫颈筛查手柄
CN117179692B (zh) * 2023-11-08 2024-04-30 苏州术客高鑫科技有限公司 一种可装载光纤导管的宫颈筛查手柄

Similar Documents

Publication Publication Date Title
US20220401603A1 (en) Apparatus and method to measure concentration of disinfectant in medical device reprocessing system
JP5652777B2 (ja) 生体センサの寿命測定システム及び方法
CN100464690C (zh) 牙垢检测系统
CA2779354C (fr) Mesure optique de la pression
US8804115B2 (en) Systems and methods for performing optical spectroscopy using a self-calibrating fiber optic probe
JP2020532369A5 (fr)
NO880891L (no) Fremgangsmaate og apparat for maaling eller deteksjon av konsentrasjonen av en substans.
CN103747732B (zh) 用于测量胆红素水平的非侵入式设备和方法
JP2002529174A (ja) 血液パラメータを測定する装置及び方法
EP2043524B1 (fr) Appareil et procédé de détection de pathologies dentaires
WO2007083991A1 (fr) Appareil et procede d'analyse optique
CN201042433Y (zh) 活体组织光学检测装置
JP6000957B2 (ja) 光学測定装置および校正方法
JP6691780B2 (ja) 成分測定装置、この装置の測定モード設定方法及びプログラム
US8842285B2 (en) Optical measurement apparatus and optical measurement system
JP2004077217A (ja) う蝕歯診断方法および装置
CN217358875U (zh) 一种内窥镜测漏预警系统
Falciai et al. Bile enterogastric reflux sensor using plastic optical fibers
CN215017477U (zh) 血氧探头和血氧检测装置
KR102000150B1 (ko) 휴대형 당 측정기
EP2042082A1 (fr) Procédé et appareil pour mesurer la fluorescence
RU35232U1 (ru) Спектральное устройство для контроля и мониторинга процесса фотодинамической терапии и лазерной флуоресцентной диагностики
JP2024095408A (ja) 蛍光検出装置
CN118304448A (zh) 用于对医疗设备进行消毒的消毒系统和方法

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application
NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 06701546

Country of ref document: EP

Kind code of ref document: A1