WO2000029872A1 - Systeme et procede de diagnostic dentaire - Google Patents

Systeme et procede de diagnostic dentaire Download PDF

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Publication number
WO2000029872A1
WO2000029872A1 PCT/US1999/027104 US9927104W WO0029872A1 WO 2000029872 A1 WO2000029872 A1 WO 2000029872A1 US 9927104 W US9927104 W US 9927104W WO 0029872 A1 WO0029872 A1 WO 0029872A1
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WO
WIPO (PCT)
Prior art keywords
intra
signal
light
oral sensor
digital signal
Prior art date
Application number
PCT/US1999/027104
Other languages
English (en)
Inventor
Sammy M. Saadia
Michael R. Matalon
Robert A. Lerner
Original Assignee
Samalon Technologies
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 Samalon Technologies filed Critical Samalon Technologies
Priority to AU21506/00A priority Critical patent/AU2150600A/en
Publication of WO2000029872A1 publication Critical patent/WO2000029872A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/58—Testing, adjusting or calibrating thereof
    • A61B6/582—Calibration
    • A61B6/583—Calibration using calibration phantoms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4423—Constructional features of apparatus for radiation diagnosis related to hygiene or sterilisation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/51—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for dentistry
    • A61B6/512—Intraoral means
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/36—Measuring spectral distribution of X-rays or of nuclear radiation spectrometry
    • G01T1/40—Stabilisation of spectrometers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0088—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for oral or dental tissue

Definitions

  • the present invention relates to system and method for providing a dental diagnosis.
  • the dental diagnosis can be determined using information about a condition of the patient's mouth (e.g., teeth, gums, oral cavity, etc.) . Such information may be obtained using a conventional dental film technology.
  • the dental film technology utilizes an X-ray apparatus and expensive chemicals for developing a dental film.
  • the dental film technology is time and labor consuming.
  • the dental film has a low sensitivity which requires the dentist to increase and/or repeat an application of an X- ray radiation (e.g., in case of the dental film's failure). Consequently, the patient is exposed to unnecessary doses of the X-ray radiation and there is an unproductive loss of time for the dentist and the patient.
  • the senor should be calibrated. Such calibration requires an activation of the X-ray apparatus and exposure of the patient to the X-ray radiation. In some cases, the calibration must be repeated a number of times until the satisfactory image can be developed. However, the patient would again be exposed to the X-ray radiation. In addition, there would be an unnecessary loss of time for the dentist and for the patient.
  • U.S. Patent No. 5,331,166 describes an automatic control system which controls the X-ray radiation using detecting elements. These detecting elements are located in the sensor which measures a value of a signal having a particular X-ray intensity. However, this control system does not prevent the unnecessary X-ray radiation received by the patient. In addition, this conventional procedure is not safe because it is executed during an activation of the X-ray apparatus.
  • U.S. Patent No. 5,434,418 describes an intra-oral sensor which uses a plurality of glass fiber bundles to transfer a light signal from a scintillator surface to a CCD.
  • a level of the signal is reduced due to high complexities in retaining a quality optical contact between the surface of the scintillator crystal and the CCD.
  • areas of conjugation at the surfaces of the scintillator crystal and the CCD are not equal.
  • U.S. Patent No. 5,723,865 describes another X-ray apparatus in which the light signal from the scintillator is transferred to the CCD using an imaging lens.
  • technical parameters and dimensions of this conventional X-ray apparatus do not enable its use for intra-oral dental applications.
  • U.S. Patent No. 5,691,539 describes a conventional intra- oral X-ray sensor which has a rectangular housing. An electrical cable with a connector is joined to a back portion of the housing coupled to an image processing unit.
  • an image processing unit is extremely uncomfortable for the patient because its shape does not conform to a dental arch and a natural jaw curve of the patient.
  • long cables from the sensor to the image processing unit irritates the patient and is inconvenient for the dentist and the patient.
  • a conventional intra-oral camera system e.g., AcuCam ®
  • the intra- oral camera system may analyze a cavity of a mouth to produce video images.
  • an application of this intra-oral camera system requires an additional equipment connected to the X-ray apparatus.
  • the video images produced by this conventional intra-oral camera system cannot be browsed nor compared with other images produced using different hardware elements and/or software modules.
  • the present invention relates to an intra-oral sensor for providing a dental diagnosis.
  • the sensor includes an arrangement receiving an external signal and converting the external signal into a light beam.
  • the sensor further includes a light reflective layer and a light concentrating element (e.g., a lens) concentrating the light beam into the concentrated light beam.
  • a particular layer e.g., a Charge Coupled Device ["CCD”] or Complementary Metal-Oxide Semiconductor ["CMOS”] array
  • the sensor includes an electronic circuitry converting the analog signal into a digital signal, the digital signal providing data for the dental diagnosis .
  • the present invention also relates to a method for providing the dental diagnosis.
  • An internal light device is activated to generate a light signal.
  • an amplification level of an amplifier of the intra-oral sensor is adjusted as a function of a predetermined correction value.
  • the light signal is detected and converted into the digital signal as a function of the adjusted amplification level. If the internal light device is activated, then if a signal value of the digital signal is not equal to a predetermined reference level, then the predetermined correction value is modified as a function of the predetermined reference level and the signal value until the signal value is equal to the predetermined reference level.
  • the digital signal provides data for the dental diagnosis .
  • Figure 1 shows an exemplary embodiment of a system providing a dental diagnosis according to the present invention.
  • Figure 2 shows a block diagram of an exemplary embodiment of an electronic arrangement provided in a computing device of the system.
  • Figure 3a shows a prospective view of an exemplary embodiment of a sensor according to the present invention utilized with the system illustrated in Figure 1.
  • Figure 3b shows a left side view of the sensor illustrated in Figure 3a.
  • Figure 3c shows a front side view of the sensor illustrated in Figure 3a.
  • Figure 3d shows a top view of the sensor illustrated in Figure 3a.
  • Figure 4a shows a prospective view of an alternative exemplary embodiment of the sensor according to the present invention which has coatings .
  • Figure 4b shows a left side view of the sensor illustrated in Figure 4a.
  • Figure 4c shows a front side view of the sensor illustrated in Figure 4a.
  • Figure 4d shows a top view of the sensor illustrated in Figure 4a.
  • Figure 5 shows an exemplary embodiment of a cable-retractable device according to the present invention which may be coupled to the sensor illustrated in Figures 3a-3d and 4a-4d.
  • Figure 6a shows a cross-section view of an exemplary embodiment of the sensor taken along line A-A as illustrated in Figures 3a and 4a.
  • Figure 6b shows a cross-section view of an alternative exemplary embodiment of the sensor taken along line A-A as illustrated in Figures 3a and 4a.
  • Figure 7a shows an enlarged view of a section of the sensor taken in an exemplary area C illustrated in Figure 6a.
  • Figure 7b shows an enlarged view of a section of the sensor taken in an exemplary area D illustrated in Figure 6b.
  • Figure 8 shows a top view of a light sensitive array of the sensor taken along line B-B as illustrated in Figures 6a and 6b.
  • Figure 9a shows a block diagram of an exemplary embodiment of an electronic arrangement of the sensor according the present invention illustrated in Figures 6a and 6b.
  • Figure 9b shows a block diagram of another exemplary embodiment of the electronic arrangement of the sensor according the present invention illustrated in Figures 6a and 6b.
  • Figure 10a shows a first exemplary flow chart illustrating a method according to the present invention.
  • Figure 10b shows a second exemplary flow chart illustrating the method according to the present invention.
  • Figure 10c shows a third exemplary flow chart illustrating the method according to the present invention.
  • Figure 11a shows a graph illustrating a coefficient of amplification for an amplifier of the sensor according to the present invention.
  • Figure lib shows another graph illustrating a reference level of the internal light signal for the amplifier as a function of time.
  • Figure 12 shows an exemplary table for analyzing an incoming signal using a remote digital unit.
  • FIG 1 shows an exemplary embodiment of a system 100 according to the present invention.
  • the system 100 allows a user (e.g., a dentist or a dental assistant) to obtain a comprehensive information about patient's mouth in a safe, expedient and convenient manner .
  • a preferred embodiment of the system 100 includes an intra-oral sensor 1, a remote digital unit ("RDU") 18, an external signal device (“ESD”) 34 and a computing device 22.
  • the ESD 34 may be, e.g., an X-ray apparatus or an Infrared apparatus.
  • the system 100 may also include a video apparatus and/or an audio apparatus to record an examination of the patient.
  • the audio apparatus may be positioned inside or outside of the system 100.
  • a plurality of the systems 100 may also be coupled together to form a dedicated network (e.g., a local area network or a wide area network) .
  • the system 100 may further be connected to a communication network (e.g., the Internet).
  • a communication network e.g.,
  • the sensor 1 is calibrated using an Internal Light Device 8 ("ILD") which is provided inside the sensor 1.
  • ILD Internal Light Device 8
  • the ILD 8 is deactivated and the ESD 34 is activated.
  • the ESD 34 generates an external signal (e.g., an X-ray radiation, an Infrared emission, etc.) which is detected by the sensor 1 and converted into a digital signal.
  • This digital signal is then provided, via an electrical cable 3, to the RDU 18.
  • the RDU 18 determines a type of an apparatus that is transmitting the digital signal and then forwards the digital signal to the computing device 22 for processing (e.g., displaying on a display device, etc.) . Details of this operation are described below.
  • FIG. 2 shows an exemplary embodiment of the computing device 22 (e.g., a personal computer).
  • the computing device 22 may include an input device 28, an output device 30, a controller 26, a memory unit 23, a first interface unit 27 and a second interface units 29.
  • the above-described elements of the computing device 22 are connected to a bus 31.
  • the input device 28 may include, e.g., a keyboard, a keypad, a scanner, a disk drive (e.g., floppy, CD or DVD), a voice recognition device, etc.
  • the user may be able to scan images from a film into the memory unit 23 in order to store a complete patient record in a digital form.
  • the output device 30 may include, e.g., a high-resolution display, a printer, a disk writer, a projector and/or another conventional output device.
  • the first interface unit 29 facilitates a connection between the computing device 22 and the RDU 18, and the second interface unit 27 facilitates a connection between the computing device 22 and at least one of the dedicated network and the communication network.
  • Figures 3a-d show a first exemplary embodiment of the sensor 1 according to the present invention.
  • the sensor 1 has a preferably flat-convex shape which is designed to fit natural contours of the patient's mouth and teeth.
  • One of the advantages of such shape is that it allows a deep and tight reach into subgingival areas as a parallel orientation is assumed.
  • the sensor 1 has a rectangular shape, however other shapes are also conceivable (e.g., square, circular, oval, etc.).
  • the sensor 1 has the case 14 and an edge portion 1A disposed thereon.
  • the case 14 hermetically encloses the elements of the sensor 1.
  • the case 14 is composed of a soft and force-absorbent material (e.g., a thermosetting hygienic protective rubber material) so that the sensor 1 would not be damaged if the patient applied pressure on the sensor 1.
  • the edge portion 1A is preferable situated on a side of the case 14 and is also composed of a soft material.
  • the material of the edge portion 1A is softer that the material of the case 14 and can include a sponge-like material. The sponge like material would protect the patient's mouth against scratched and/or abrasions which may occur otherwise during the use of the sensor 1.
  • the case 14 provides a rugged, shatterproof finish which is immune to a shock and/or a bite of the patient .
  • a top wall of the case 14 is composed of a material which allows the external signal to pass therethrough.
  • Other walls of the case 14 are composed of a material absorbing the external signal (e.g., the material including an additive of lead, tungsten and/or bismuth) . Since a sterilization process of the sensor 1 requires utilization of a high temperature, the sensor 1 is not autoclaved to prevent negative effects of such high temperature on a particular layer 10 (e.g., a CCD array or a CMOS array) . Therefore, the sensor 1 may utilize a custom fitted plastic sheaths or a disposable latex coating for an infection control .
  • Figures 4a-d shows a second exemplary embodiment of the sensor 1' according to the present invention.
  • the sensor 1' of the second embodiment has identical elements as described above for the sensor 1 of the first embodiment.
  • this sensor 1' has at least one (preferably 2 or 4) coating 121 situated preferable at corners of a housing 6 of the sensor 1' .
  • This coating 121 includes a filler material which is composed mostly of a softly protective material (e.g., polypropylene or polyethylene) .
  • the filler material is an inert granular material being composed of small particles which are mixed into a plastic material prior to molding.
  • the coating 121 may include a sterile material such as polyvinyltolnence and/or methacrylate-styrene copolymers . These materials are self-sterilizing and may include an anti- microbial solution.
  • the sensor 1 is coupled, via the electrical cable 3, to a connecting plug 4.
  • Figure 5 shows a detailed illustration of the connecting plug 4 which may be coupled to the RDU 18 and/or to the computing unit 22.
  • the connecting plug 4 includes a cable-retractable device ("CRD") 2 which allows the user to retract the electric cable 3 within a housing 120 of the connecting plug 4.
  • a circuit interface unit 21 of the sensor 1 may include a wireless remote unit (“WRU") (not illustrated) instead of the connecting plug 4 and the electrical cable 3.
  • WRU wireless remote unit
  • This WRU may transmit the signal (e.g., a radio-frequency signal) to the RDU 18 and/or to the computing device 22.
  • the RDU 18 and/or the first interface unit 26 of the computing unit 22 may also include the WRU.
  • Figure 6a shows a cross-sectional view of the sensor 1, taken along line A-A as illustrated in Figures 3a and 4a.
  • the sensor 1 includes the water-resistant housing 6 enclosed by a case 14. Inside of the housing 6, at least one internal light device (“ILD") 8 is situated within a crystal 5 (i.e., a converting element) .
  • Figure 7a shows an exemplary area C of the sensor 1 where a light concentrating element (e.g., a micro lens, a concentric lens [see, e.g., Figures 6b and 7b], etc.) 9 is situated between the crystal 5 and the particular layer 10.
  • the particular layer 10 is situated on a top layer 11 which is attached to a silicon substrate 12.
  • a plurality of pins 13 are positioned below the silicon substrate 12 and are coupled to the electrical cable 3.
  • the crystal 5 is capable of converting the external signal into a corresponding light beam.
  • the crystal 5 When exposed to the X-ray radiation as the external signal, the crystal 5 is configured as a scintillator which is composed of a single optically transparent mono crystal (e.g., CsI(Tl) or Nal(Tl)).
  • a single optically transparent mono crystal e.g., CsI(Tl) or Nal(Tl)
  • at least one of the crystal 5 and the particular layer 10 may be composed of
  • the crystal 5 preferably has a predetermined shape (e.g., a flat shape at a bottom portion of the crystal 5 and a convex shape at a top portion of the crystal 5) and a predetermined thickness (e.g., no more than 500 micron).
  • a predetermined shape e.g., a flat shape at a bottom portion of the crystal 5 and a convex shape at a top portion of the crystal 5
  • a predetermined thickness e.g., no more than 500 micron.
  • the crystal 5 When using the Infrared emission as the external signal, the crystal 5 is preferably composed of a thermo-illuminating material and converts the external signal (i.e., the Infrared emission) into the light beam.
  • a light reflective layer 7 of the sensor 1 includes an Infrared transparent light concentrating element composed of silicon and/or germanin.
  • the top portion of the housing 6 has a convex shape. It is preferable for a top portion of the sensor 1 to be tightly pressed to the teeth.
  • the convex shape which follows the natural curve of the jaw, may increase a quality of the image.
  • the housing 6 (which situates the crystal 5 therein) has a light-opaque feature.
  • the housing 6 prevents the external signal from entering or exiting the housing 6 on sides 131-135 (shown in Figures 6a, 6b and 8) of the housing 6.
  • the external signal can enter the housing 6, but not exit.
  • the top side 130 is preferably positioned, as shown in Figure 6a, above the crystal 5.
  • the light reflective layer 7 of the housing 6 which is situated on an internal side of the top side 130, as shown in Figure 5a.
  • the light reflective layer 7 is composed of, e.g., silver or aluminum.
  • the light reflective layer 7 is capable of completely reflecting the light beam emitted by the crystal 5.
  • a surface of the light reflective layer 7 does not allow the light beam to be dissipated by the crystal 5 in different directions, and concentrates the light beam toward the particular layer 10 (e.g., toward matrix light sensitive elements of the CCD array or the CMOS array) .
  • the light reflective layer 7 has a thickness of preferably no more than 30 micron; however, other thicknesses are conceivable.
  • the ILD 8 of the sensor 1 is utilized to calibrate the system 100 by providing the light beam which is representative of a standard value (e.g., a predefined value) of illumination.
  • the ILD 8 is provided within the crystal 5 and is positioned along one of the second and third sides 131, 132 of the housing 6, below the first side 130.
  • the ILD 8 may include at least one light emitting diode (e.g., preferably two, four, six, eight, etc.) .
  • two ILDs 8 are situated opposite one another along a horizontal symmetry axis X-X.
  • the light concentrating element 9 preferably includes a flat-convex converging micro-lens which provides a high quality optical contact between the crystal 5 and the particular layer 10.
  • the light concentrating element 9 operates as a magnifier to magnify the light beam emitted from the crystal 5 and to improve a contrast sensitivity and details of the image.
  • the light concentrating element 9 is composed of a highly absorbing material which absorbs the scattered external signal and does not generate a secondary exposure (e.g., a secondary scale of radiation) .
  • a secondary exposure e.g., a secondary scale of radiation
  • Such material may be, e.g., a glass material or a plastic material, with an additive material (e.g., lead, tungsten and/or bismuth) .
  • the light concentrating element 9 has a flat shape. Such a flat shape allows the sensor 1 to be thinner and more comfortable for the patient.
  • the light concentrating element 9 has a concentric relief 140 (i.e., a surface) for concentrating the light beam, which has a preferably stepped shape.
  • the particular layer 10 is utilized to convert the light beam into an analog signal.
  • the particular layer 10 may include the CCD and/or the CMOS matrix of the light sensitive elements as shown in Figure 8.
  • the bottom layer 11 includes an electronic integrated circuit 150.
  • Figure 9a shows an exemplary embodiment of this electronic integrated circuit 150.
  • the circuit 150 may include a programmable, low-noise amplifier 15, a peak comparator 16 (which establishes a threshold level) , an analog-to-digital converter ("A/D") 17, a digital-to-analog converter ("D/A”) 19, a memory unit 20 and a circuit interface unit 21. Functions of these elements of the circuit 150 are described below.
  • An alternative exemplary embodiment of the sensor 1 may include at least one controller 32 shown in Figure 9b. This controller 32 may perform all necessary operations to calibrate and utilize the system 100 without requiring the use of the computing device 22.
  • the controller 32 is, preferably, positioned inside of the sensor 1; alternatively, the controller 32 may be positioned outside of the sensor 1.
  • an alternative embodiment of the system 100 according to the present invention may include the sensor 1 having the above-described controller 32, the RDU 18, the ESD 34 and the output device 30.
  • FIG. 10a shows a first exemplary flow chart of the method according to the present invention.
  • a reference level RL and a prime value K may be preset (steps 905 and 910) by a manufacturer of the sensor 1 and/or by the user.
  • the reference level RL and the prime value K may be stored in the memory unit 20 of the sensor 1 and may be reset each time the system 100 is activated.
  • the reference level RL and the prime value K may be stored in the memory unit 23 of the computing device 22.
  • the computing device 22 transmits the reference level RL and the prime value K to the sensor 1 when the system 100 is activated or when the user desires to do so.
  • the threshold level remains in the memory unit 20.
  • the comparator 16 establishes the threshold level which is higher than a signal-to-noise ration of the particular layer 10 (e.g., a dark current shown in Figure 11B) .
  • the user activates the ILD 8 (step 915) .
  • An amplification level of the amplifier 15 is adjusted as a function of the prime value K (step 917) .
  • the ILD 8 generates the light beam within the crystal 5.
  • the light concentrating element 9 focuses the light beam onto the particular layer 10.
  • the particular layer 10 detects the light beam as an analog signal (step 920) and the amplifier 15 amplifies this analog signal.
  • the comparator 16 filters the analog signal using the value of the threshold level; only relevant part of the analog signal (i.e., a portion which has the optimal signal-to-noise ration shown in Figure lib) passes through the comparator 16.
  • This portion of the analog signal is converted into the digital signal using the A/D convertor 17 (step 925) .
  • the digital signal is transmitted to the RDU 18 via the circuit interface unit 21.
  • the RDU 18 forwards the digital signal to the computing device 22.
  • the computing device 22 determines whether the ILD 8 (or the ESD 34) is activated (step 930) . If the ILD 8 is activated, that indicates that the system 100 is in a calibration (i.e., testing) mode and the digital signal is the ILD signal. Thus, the computing device 22 may display the image which is representative of the ILD signal on the output device 30 (step 935) . A value of the digital signal is then compared to the value of the reference level RL (step 940) . If the value of the digital signal is not equal to the value of the reference level RL as shown in Figure lib, then the prime value K must be adjusted (see a value K_ and a value K 2 in Figure 11a) .
  • the computing device 22 adjusts the prime value K as a function of the value of the digital signal and of the value of the reference level RL (step 945) .
  • the prime value K is transmitted back to the sensor 1 via the RDU 18 and stored in the memory unit 20 of the sensor 1.
  • the steps 917- 945 are repeated until the digital signal is equal to the value of the reference level RL.
  • the calibration mode is completed and the system 100 is ready to initiate an execution mode (step 950) .
  • the user deactivates the ILD 8 and activates the ESD 34 (step 955) which generated an ESD signal (e.g., the X-ray radiation or the Infrared emission) .
  • the amplification level of the amplifier 15 is then adjusted as a function of the prime value K (step 917) . Therefore, the ESD signal is detected and converted into the light beam using the crystal 5. This light beam is converted into the analog signal using the particular layer 10 and the amplifier 15 (step 920) .
  • the analog signal is converted into the digital signal (step 925) using the A/D converter 17.
  • the image which is representative of the ESD signal may be stored and/or displayed (step 960) using the output device 30.
  • the output device 30 may facilitate a storage of the digital signal by printing the image using the printer, by storing the image on a CD ROM disk or in a memory storage unit of a network server, or by transmitting the image to a predetermined location via the communication network.
  • the user can also bypass the calibration mode (step 936) .
  • the user may calibrate the system 100 manually or automatically (step 937) .
  • the user manually adjusts the prime value K (step 938) by checking the image using the output device 30 and adjusting it using the input device 28. If manual calibration is not desired, the computing device 22 performs "an automatic" calibration as described above for Figure 10a (steps 940-945) .
  • the system 100 is calibrated in another manner.
  • the external signal is detected (step 917)
  • the external signal is converted into the digital signal (step 920) .
  • the digital signal is adjusted as a function of the prime value K (step 925) .
  • the system 100 includes the sensor 1 which has the controller 32, as described above. This controller 32 allows the manual calibration and/or automatic calibration of the system 100, with or without the computing device 22.
  • a plurality of apparatuses may be connected to the RDU 18, e.g., the X-ray apparatus, the Infrared apparatus, the video apparatus and/or the audio apparatus.
  • the audio apparatus may be positioned inside and/or outside of the system 100. Since of each of these four apparatuses transmits respective signals, the RDU 18 is capable to record each of such signals.
  • Figure 11 shows an exemplary chart that allows the RDU 18 to determine from which apparatus is a received signal originated from using a predetermined binary code. In particular, each apparatus is assigned a predetermined binary code and a corresponding connector number.
  • the RDU 18 interprets the signals from these apparatuses as a function of the predetermined binary codes and connector numbers (e.g., the X- ray apparatus has a binary code "00" and is assigned to XP1 connector) and forwards a corresponding message to the computing device 22 identifying a type of the signal being transmitted.
  • the RDU 18 may be situated in a close proximity to the patient.
  • the RDU 18 may be situated near a top portion of a dental chair as shown in Figure 1.
  • An advantage of utilizing the RDU 18 in such manner is that a number of wires within a dental office can be reduced.
  • the system 100 may include the audio and video apparatuses .
  • the video apparatus allows the system 100 to capture a video image while the audio apparatus allows the system 100 to record comments from the user and/or the patient during the examination of the patient.
  • the video and audio recordings are then converted into a digital form and linked to the image generated by the ESD 34.
  • a single digital file may contain the ESD image and the video and audio recordings. This file may be maintained by the user, the patient or a predetermined databank.
  • One of the advantages of the present invention is that the patient's exposure to radiation (e.g., the X-ray radiation) is reduced by eliminating risk of unsatisfactory images due to a failure of the equipment or in an properly adjusted equipment. Thus, the image has a high resolution and clarity without risking image failures and unnecessary X-ray activations do not have to be performed.
  • the light concentrating element 9 (either on its own or together with the light reflective layer 7) strongly converges and concentrates the light beams from the crystal 5 to generate, using the particular layer 10, a crisp image with increased brightness, high resolution and clarity.
  • a further advantage of the present invention is that the retractable CRD 2 of the connecting plug 4 can be utilized.
  • This CRD 2 avoids an irritation of the patient's mouth by the sensor 1.
  • An absence of a long cable provides comfort by positioning the sensor 1 in the mouth without any hanging cords .
  • controller 32 of the sensor 1 makes the system 100 faster and more reliable.
  • controller 32 frees the resources of the computing device 22 and simplifies an interface between the sensor 1, the RDU 18 and the computing unit 22.

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  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Mathematical Physics (AREA)
  • General Physics & Mathematics (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Apparatus For Radiation Diagnosis (AREA)

Abstract

La présente invention concerne un capteur intraoral (1) destiné au diagnostic dentaire. Le capteur comprend un arrangement recevant un signal externe et convertissant (5) le signal externe en un faisceau lumineux. Le capteur comprend, en outre, une couche réfléchissant la lumière (7) et un élément concentrateur de lumière (9) permettant de concentrer le faisceau lumineux. Une couche particulière (10) (par exemple, une matrice à circuit à couplage de charges « CCD » ou à semi-conducteur « CMOS ») reçoit le faisceau lumineux concentré et le convertit en un signal analogique. Une procédure d'étalonnage permet d'étalonner le capteur. Un dispositif lumineux interne (8) du capteur est activé en vue de générer un signal lumineux. Puis un niveau d'amplification d'un amplificateur du capteur intraoral est ajusté en fonction d'une valeur corrective prédéterminée. Le signal lumineux est détecté et converti en signal numérique en fonction du niveau d'ajustement d'amplification.
PCT/US1999/027104 1998-11-17 1999-11-12 Systeme et procede de diagnostic dentaire WO2000029872A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU21506/00A AU2150600A (en) 1998-11-17 1999-11-12 System and method for providing a dental diagnosis

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US19355598A 1998-11-17 1998-11-17
US09/193,555 1998-11-17

Publications (1)

Publication Number Publication Date
WO2000029872A1 true WO2000029872A1 (fr) 2000-05-25

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Family Applications (1)

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PCT/US1999/027104 WO2000029872A1 (fr) 1998-11-17 1999-11-12 Systeme et procede de diagnostic dentaire

Country Status (2)

Country Link
AU (1) AU2150600A (fr)
WO (1) WO2000029872A1 (fr)

Cited By (9)

* Cited by examiner, † Cited by third party
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WO2002077667A1 (fr) * 2001-03-23 2002-10-03 Koninklijke Philips Electronics N.V. Procede de determination de la quantite de rayonnement absorbee par un detecteur de rayonnement
EP1378201A1 (fr) * 2002-07-05 2004-01-07 Cefla Soc. Coop. A R.L. Dispositif d'acquisition et d'affichage des images radiographiques dentaires
FR2876572A1 (fr) * 2004-10-18 2006-04-21 Visiodent Sa Equipement de prise de vue dentaire
EP1649812A1 (fr) 2004-10-15 2006-04-26 ELCA TECHNOLOGIES S.r.l. Dispositif et méthode d'acquisition et d'affichage sans fil d'images radiographiques dentaires
WO2006103126A1 (fr) * 2005-04-01 2006-10-05 E2V Semiconductors Capteur d'image dentaire intra-oral et systeme radiologique utilisant ce capteur
EP1829482A1 (fr) * 2003-11-21 2007-09-05 Eastman Kodak Company Appareil de radiologie dentaire et procédé de traitement de signal utilisé correspondant
FR2915079A1 (fr) * 2007-04-20 2008-10-24 E2V Semiconductors Soc Par Act Capteur d'image radiologique dentaire avec surmoulage souple
CN106725588A (zh) * 2017-01-18 2017-05-31 佛山市邦宁电子科技有限公司 一种便携式牙科x光传感器及牙科x光成像方法
KR20190055399A (ko) * 2017-11-15 2019-05-23 (주)해우기술 엑스레이 디텍터 제어장치 및 그 방법

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US5237173A (en) * 1992-04-01 1993-08-17 Independent Scintillation Imaging Systems, Inc. Gain calibration in a scintillation camera
US5331166A (en) * 1991-10-25 1994-07-19 Kabushiki Kaisha Morita Seisakusho Dental X-ray image detecting device with an automatic exposure function

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5331166A (en) * 1991-10-25 1994-07-19 Kabushiki Kaisha Morita Seisakusho Dental X-ray image detecting device with an automatic exposure function
US5237173A (en) * 1992-04-01 1993-08-17 Independent Scintillation Imaging Systems, Inc. Gain calibration in a scintillation camera

Cited By (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009042233A (ja) * 2001-03-23 2009-02-26 Koninkl Philips Electronics Nv 放射線センサによって吸収される照射線量を決定する方法
US6840674B2 (en) 2001-03-23 2005-01-11 Koninklijke Philips Electronics N.V. Method of determining the quantity of radiation absorbed by a radiation sensor
WO2002077667A1 (fr) * 2001-03-23 2002-10-03 Koninklijke Philips Electronics N.V. Procede de determination de la quantite de rayonnement absorbee par un detecteur de rayonnement
EP1378201A1 (fr) * 2002-07-05 2004-01-07 Cefla Soc. Coop. A R.L. Dispositif d'acquisition et d'affichage des images radiographiques dentaires
US8319190B2 (en) 2003-11-21 2012-11-27 Carestream Health, Inc. Dental radiology apparatus and signal processing method used therewith
US8481954B2 (en) 2003-11-21 2013-07-09 Carestream Health, Inc. Dental radiology apparatus and signal processing method used therewith
EP1829482A1 (fr) * 2003-11-21 2007-09-05 Eastman Kodak Company Appareil de radiologie dentaire et procédé de traitement de signal utilisé correspondant
US8481955B2 (en) 2003-11-21 2013-07-09 Carestream Health, Inc. Dental radiology apparatus and signal processing method used therewith
US7608834B2 (en) 2003-11-21 2009-10-27 Carestream Health, Inc. Dental radiology apparatus and signal processing method used therewith
US8481956B2 (en) 2003-11-21 2013-07-09 Carestream Health, Inc. Dental radiology apparatus and signal processing method used therewith
US8008628B2 (en) 2003-11-21 2011-08-30 Carestream Health, Inc. Dental radiology apparatus and signal processing method used therewith
EP1649812A1 (fr) 2004-10-15 2006-04-26 ELCA TECHNOLOGIES S.r.l. Dispositif et méthode d'acquisition et d'affichage sans fil d'images radiographiques dentaires
US7505558B2 (en) 2004-10-15 2009-03-17 Elca Technologies S.R.L. Apparatus for acquiring and visualizing dental radiographic images and operating method thereof
FR2876572A1 (fr) * 2004-10-18 2006-04-21 Visiodent Sa Equipement de prise de vue dentaire
FR2883719A1 (fr) * 2005-04-01 2006-10-06 Atmel Grenoble Soc Par Actions Capteur d'image dentaire intra-oral et systeme radiologique utilisant ce capteur
WO2006103126A1 (fr) * 2005-04-01 2006-10-05 E2V Semiconductors Capteur d'image dentaire intra-oral et systeme radiologique utilisant ce capteur
WO2008135348A1 (fr) * 2007-04-20 2008-11-13 E2V Semiconductors Capteur d'image radiologique dentaire avec surmoulage souple
US7972060B2 (en) 2007-04-20 2011-07-05 E2V Semiconductors Dental radiology image sensor with soft overmolding
FR2915079A1 (fr) * 2007-04-20 2008-10-24 E2V Semiconductors Soc Par Act Capteur d'image radiologique dentaire avec surmoulage souple
CN106725588A (zh) * 2017-01-18 2017-05-31 佛山市邦宁电子科技有限公司 一种便携式牙科x光传感器及牙科x光成像方法
CN106725588B (zh) * 2017-01-18 2021-02-05 佛山市邦宁电子科技有限公司 一种便携式牙科x光传感器及牙科x光成像方法
KR20190055399A (ko) * 2017-11-15 2019-05-23 (주)해우기술 엑스레이 디텍터 제어장치 및 그 방법
KR101997826B1 (ko) 2017-11-15 2019-07-08 (주)해우기술 엑스레이 디텍터 제어장치 및 그 방법

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