WO2008119964A1 - A non-ionising imager - Google Patents

A non-ionising imager Download PDF

Info

Publication number
WO2008119964A1
WO2008119964A1 PCT/GB2008/001085 GB2008001085W WO2008119964A1 WO 2008119964 A1 WO2008119964 A1 WO 2008119964A1 GB 2008001085 W GB2008001085 W GB 2008001085W WO 2008119964 A1 WO2008119964 A1 WO 2008119964A1
Authority
WO
WIPO (PCT)
Prior art keywords
imager
radiation
light
sample
source
Prior art date
Application number
PCT/GB2008/001085
Other languages
French (fr)
Other versions
WO2008119964A8 (en
Inventor
John Michael Girkin
Simon Poland
Christopher Longbottom
Original Assignee
University Of Strathclyde
The University Court Of The University Of Dundee
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 University Of Strathclyde, The University Court Of The University Of Dundee filed Critical University Of Strathclyde
Priority to EP08718915A priority Critical patent/EP2131722A1/en
Priority to US12/594,095 priority patent/US9084535B2/en
Publication of WO2008119964A1 publication Critical patent/WO2008119964A1/en
Publication of WO2008119964A8 publication Critical patent/WO2008119964A8/en

Links

Classifications

    • 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
    • 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
    • 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
    • G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
    • 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
    • G01N2021/4704—Angular selective
    • G01N2021/4707—Forward scatter; Low angle scatter
    • 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
    • G01N2021/4704—Angular selective
    • G01N2021/4711—Multiangle measurement
    • G01N2021/4719—Multiangle measurement using a optical fibre array
    • 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
    • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
    • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
    • G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
    • G01N21/359—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light using near infrared light
    • 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
    • G01N2201/10—Scanning
    • G01N2201/105—Purely optical scan
    • G01N2201/1053—System of scan mirrors for composite motion of beam
    • 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
    • G01N2201/10—Scanning
    • G01N2201/108—Miscellaneous
    • G01N2201/1085—Using optical fibre array and scanner

Definitions

  • the present invention relates to a non-ionising imager, primarily for use in oral and dental, medical and veterinary applications.
  • the present invention relates to an infrared or near infrared imager.
  • X-rays are widely used for dental assessment of the developing occlusion and tooth structure.
  • X-ray imaging carries with it well known health hazards and the dosage has to be kept within defined limits. This means that it is generally not possible for clinicians to take multiple images.
  • the health hazards are a particular problem for young patients, who may be more sensitive to the negative effects of X- ray exposure.
  • Wist et al developed an imager for imaging individual teeth using a point-scanned system, see for example "A new
  • a non-scanning medical imager that has a source for providing a plurality of collimated beams of non-ionising radiation and a plurality of correlated detectors, each detector being arranged to receive unscattered light from one or part of one of said collimated beams and scattered light from one or more other beams.
  • the imager is preferably operable to distinguish between the unscattered and scattered light.
  • the imager may further comprise means for using both the unscattered and scattered light to form an image.
  • the present invention offers the ability to take multiple high-resolution images giving the same or better information, without the hazard of multiple exposures to X-ray.
  • this opens up the possibility of routine imaging of every tooth at every dental check-up, which could improve early detection of caries and facilitate optimal preventive and operative therapy. It also allows for the imaging of the jaws for the developing dentition, which would be of enormous clinical benefit in children's and orthodontic assessments, as well as monitoring tissue during endo-dontic and periodontal therapy.
  • the source may be laser, LED or thermal source and may be pixelated or be directed onto a device that produces an array of "beamlets". Each beamlet is correlated with a pixelated or point scanned detector, so that it would be expected to land on one or more corresponding pixels if there was no deviation of the beamlet between the source and detector.
  • All of the individual beamlets or patterns may be switched on simultaneously for complete coverage of the sample. Alternatively, one or more selected groups of pixels may be switched on.
  • the non-ionising radiation is infrared radiation.
  • Light around 810nm may be used. This has advantages for oral and dental applications in that it can be well transmitted through teeth but undergoes sufficient scattering if a change in the optical properties of the tooth, for example, is present. Radiation having a wavelength of 810nm is also well detected by Si based detectors offering the possibility of low cost and light efficient systems.
  • Light may be used to undertake differential spectroscopic imaging to distinguish oxygenated and de-oxygenated blood.
  • the light for doing this may be in the range of around 810nm and 850nm.
  • the use of wavelengths for identifying and quantifying the presence of blood and/or small blood vessels in particular regions of an image may be of value in identifying regions of inflammation, thereby indicating potential areas of pathological change.
  • a preferred wavelength range is HOOnm to 1300nm. Wavelengths for imaging bone, muscle, skin and other soft tissues are in the NIR, to allow imaging of the jaws.
  • the light may be temporally coherent or not, although spatial coherence may need to be removed to prevent problems on the detector.
  • One or more filters may be used with the source to preferentially select the incident light.
  • the one or more filters may be used with the detector to remove background light.
  • the light source and or detector may be located some distance from the object to be imaged where suitable means can be used to transmit the beamlets to and/or from the points on either side of the object.
  • suitable means can be used to transmit the beamlets to and/or from the points on either side of the object.
  • the system could be used endoscopically with arrayed fibres delivering and/or receiving the light from a remote source/detector. These fibres need not be a coherent bundle as fibre emission can be "mapped" onto the detector.
  • the part of the human or animal body is a tooth.
  • Figure 1 shows a non- ionising, non-scanning imager.
  • Figure 1 shows a non-ionising, non-scanning imager that is capable of projecting an array of collimated infrared beamlets onto a detector. This allows imaging of, and or through, soft tissue, bone and tooth tissue.
  • the imager of Figure 1 has a non-ionising light source that is positioned at the focal point of a collimating lens.
  • the source may be an LED, laser diode or thermal source or any other suitable non-ionising radiation source.
  • On the optical path from the lens is a digital mirror that has a plurality of individual reflecting elements or pixels.
  • the digital mirror may be of any suitable form, for example, a Texas Instruments Digital Mirror having 1076 x 756 individual mirrors each around 10 microns by 7 microns.
  • Each mirror is individually switchable between an on and off position at up to 100 kHz.
  • Light that passes through the lens is collimated and directed onto the digital mirror. With all the mirrors in the on position the complete collimated beam would be reflected to form a plurality of collimated beamlets. Alternatively, individual beamlets or selected groups of beamlets can be reflected.
  • a detector for example a CCD camera, which has a plurality of detector elements or pixels.
  • the emitter and detector are arranged such that there is correlation between the emitting and detecting pixels. This correlation is effected by coding the light using, for example, a computer.
  • the beamlets are switched on in turn and mapped to one or more detector pixels.
  • the beamlets are arranged and sized so that no detector pixel receives unscattered radiation from more than one beamlet, although a single beamlet may extend over more than one detector pixel.
  • the correlation information is then stored and used when the beamlets are activated again.
  • the correlation can be temporal as well as spatial, i.e. an image can be formed from one or more pixels.
  • a computer processor Connected to both the digital mirror and the detector is a computer processor, typically a PC, which has software for analysing the light that is reflected from each element/pixel of the digital mirror and detected signals, thereby to form an image. Because ballistic and scattered photons can be distinguished, the contrast, and hence quality of the infrared transmission images is increased.
  • a sample is placed in the space between the mirror array and the camera.
  • either the light source or the detector may be placed inside the oral cavity around the point of interest.
  • the pixels are switched on either in groups or individually. To avoid cross talk, typically adjacent groups are not switched on simultaneously.
  • the light falling on each corresponding camera pixel is then recorded and the next pixel array switched on and its corresponding signal recorded. Thus, only directly transmitted light is detected.
  • collimated beamlets enhances the local effects of scattering centres in the sample, thereby providing images with greater contrast and apparent resolution.
  • light is provided from a single high power LED, it could equally be from a laser, such as a laser diode, or from a conventional thermal light source (bulb).
  • the source could be an array of such sources such as an LED micro-array or VCSEL array, provided each beam or group of beams can be mapped onto the detector.
  • a scanning disc containing an array of holes could be used if it was known exactly which hole was present in front of the source at any one time and hence which detector pixel should be used.
  • Light at around 810nm is preferred for some oral and dental applications. Where high-resolution images of teeth are required, light in the range of llOOnm to 1300nm is preferred. However, other wavelengths could be used to potentially detect other items and to pass through other tissue types.
  • the imaging method of the present invention offers a significant increase in the contrast of IR images.
  • additional information about the scattering object is provided. For example, scattering will change as a lesion dries out and this rate of change will provide some information on the state of a carious lesion.
  • the invention provides significantly higher sensitivity to early lesions/tissue changes.
  • the invention makes it possible to image in vivo through the jaws (skin, muscle, gums and bone) to image the developing dentition, which is important in orthodontic and developmental assessments.
  • the invention makes it possible to image hard dental tissue, in vivo with high image quality.
  • the dental tissue that can be imaged includes: 1) carious lesions, including at the early stages 2) the enamel dentine junction, hence image enamel thickness and 3) the root canal system through the gum and bone, offering the possibility of continual assessment during root canal therapy.
  • Other body parts can also be imaged, such as other parts of the head and neck, as well as limbs and possibly parts of the torso. This can all be done without the need for x-rays, thereby offering significant advantages over conventional radiography in terms of health hazards.
  • the light source and or detector may be located some distance from the object to be imaged.
  • suitable means can be used to transmit the beamlets to and/or from the points on either side of the object.
  • the system could be used endoscopically with arrayed fibres delivering and/or receiving the light from a remote source/detector.
  • the invention has been described with reference to two-dimensional imaging, separate images taken at different angles could be captured and processed to generate 3-D images. Accordingly the above description of the specific embodiment is made by way of example only and not for the purposes of limitation. It will be clear to the skilled person that minor modifications may be made without significant changes to the operation described.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biophysics (AREA)
  • Engineering & Computer Science (AREA)
  • Molecular Biology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Chemical & Material Sciences (AREA)
  • Biochemistry (AREA)
  • Analytical Chemistry (AREA)
  • Immunology (AREA)
  • General Physics & Mathematics (AREA)
  • Audiology, Speech & Language Pathology (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Dental Tools And Instruments Or Auxiliary Dental Instruments (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)
  • Endoscopes (AREA)

Abstract

A medical imager, primarily for use in oral and dental applications. The imager has a source for providing a plurality of collimated beams of non-ionising radiation, in particular near-infrared light, and a plurality of correlated detectors. Each detector is arranged to receive unscattered light from one or part of one of said collimated beams and scattered light from one or more other beams. The imager further comprises means for using both the unscattered and scattered light to form an image.

Description

A Non-Ionising Imager
The present invention relates to a non-ionising imager, primarily for use in oral and dental, medical and veterinary applications. In particular, the present invention relates to an infrared or near infrared imager.
X-rays are widely used for dental assessment of the developing occlusion and tooth structure. However, X-ray imaging carries with it well known health hazards and the dosage has to be kept within defined limits. This means that it is generally not possible for clinicians to take multiple images. The health hazards are a particular problem for young patients, who may be more sensitive to the negative effects of X- ray exposure.
To avoid some of the problems with X-ray imaging, Wist et al developed an imager for imaging individual teeth using a point-scanned system, see for example "A new
Transillumination System for the Correct Assessment of Covered Caries Lesions and
Root Canals in Teeth" A O Wist, R Sterne, P Moon, Proc Spie 2329 1994. Daniel
Fried and John Featherstone have also undertaken imaging using IR light of dental tissue, see Optics Express 13 573 2005. However, neither of these systems is practical for in vivo applications due mainly to the time required to build an image and the related potential for tissue movement. In addition, the placing of scanning components in the oral cavity or elsewhere is a non-trivial challenge.
According to the present invention, there is provided a non-scanning medical imager that has a source for providing a plurality of collimated beams of non-ionising radiation and a plurality of correlated detectors, each detector being arranged to receive unscattered light from one or part of one of said collimated beams and scattered light from one or more other beams. The imager is preferably operable to distinguish between the unscattered and scattered light. The imager may further comprise means for using both the unscattered and scattered light to form an image.
By using a plurality of collimated beams of non-ionising radiation, and detecting both unscattered and scattered radiation, the present invention offers the ability to take multiple high-resolution images giving the same or better information, without the hazard of multiple exposures to X-ray. For oral and dental applications this opens up the possibility of routine imaging of every tooth at every dental check-up, which could improve early detection of caries and facilitate optimal preventive and operative therapy. It also allows for the imaging of the jaws for the developing dentition, which would be of enormous clinical benefit in children's and orthodontic assessments, as well as monitoring tissue during endo-dontic and periodontal therapy.
The source may be laser, LED or thermal source and may be pixelated or be directed onto a device that produces an array of "beamlets". Each beamlet is correlated with a pixelated or point scanned detector, so that it would be expected to land on one or more corresponding pixels if there was no deviation of the beamlet between the source and detector.
All of the individual beamlets or patterns may be switched on simultaneously for complete coverage of the sample. Alternatively, one or more selected groups of pixels may be switched on.
Preferably, the non-ionising radiation is infrared radiation. Light around 810nm may be used. This has advantages for oral and dental applications in that it can be well transmitted through teeth but undergoes sufficient scattering if a change in the optical properties of the tooth, for example, is present. Radiation having a wavelength of 810nm is also well detected by Si based detectors offering the possibility of low cost and light efficient systems.
Light may be used to undertake differential spectroscopic imaging to distinguish oxygenated and de-oxygenated blood. The light for doing this may be in the range of around 810nm and 850nm. The use of wavelengths for identifying and quantifying the presence of blood and/or small blood vessels in particular regions of an image may be of value in identifying regions of inflammation, thereby indicating potential areas of pathological change.
There may, however, be advantages in moving to longer wavelengths for some tissue types. For example, for high contrast images of teeth, a preferred wavelength range is HOOnm to 1300nm. Wavelengths for imaging bone, muscle, skin and other soft tissues are in the NIR, to allow imaging of the jaws.
The light may be temporally coherent or not, although spatial coherence may need to be removed to prevent problems on the detector.
One or more filters may be used with the source to preferentially select the incident light. The one or more filters may be used with the detector to remove background light.
For convenience the light source and or detector may be located some distance from the object to be imaged where suitable means can be used to transmit the beamlets to and/or from the points on either side of the object. This means that the system could be used endoscopically with arrayed fibres delivering and/or receiving the light from a remote source/detector. These fibres need not be a coherent bundle as fibre emission can be "mapped" onto the detector.
According to another aspect of the invention, there is provided a method of diagnosis of the human or animal body that uses images derived using the system or method of any of the preceding claims. Preferably, the part of the human or animal body is a tooth.
Various aspects of the present invention will now be described by way of example only, and with reference to the accompanying drawing, Figure 1, which shows a non- ionising, non-scanning imager.
Figure 1 shows a non-ionising, non-scanning imager that is capable of projecting an array of collimated infrared beamlets onto a detector. This allows imaging of, and or through, soft tissue, bone and tooth tissue. The imager of Figure 1 has a non-ionising light source that is positioned at the focal point of a collimating lens. The source may be an LED, laser diode or thermal source or any other suitable non-ionising radiation source. On the optical path from the lens is a digital mirror that has a plurality of individual reflecting elements or pixels. The digital mirror may be of any suitable form, for example, a Texas Instruments Digital Mirror having 1076 x 756 individual mirrors each around 10 microns by 7 microns. Each mirror is individually switchable between an on and off position at up to 100 kHz. Light that passes through the lens is collimated and directed onto the digital mirror. With all the mirrors in the on position the complete collimated beam would be reflected to form a plurality of collimated beamlets. Alternatively, individual beamlets or selected groups of beamlets can be reflected.
On the reflection path from the digital mirror is a detector, for example a CCD camera, which has a plurality of detector elements or pixels. The emitter and detector are arranged such that there is correlation between the emitting and detecting pixels. This correlation is effected by coding the light using, for example, a computer. At some point, typically at start-up with no sample between the mirror and camera, the beamlets are switched on in turn and mapped to one or more detector pixels. The beamlets are arranged and sized so that no detector pixel receives unscattered radiation from more than one beamlet, although a single beamlet may extend over more than one detector pixel. The correlation information is then stored and used when the beamlets are activated again. The correlation can be temporal as well as spatial, i.e. an image can be formed from one or more pixels.
Once the system is set up and a sample is being imaged, ballistic photons go straight through the sample to the mapped pixel or pixels, and scattered light is diverted into others. Because each detector pixel is set up to receive unscattered radiation from only a single beamlet, scattered radiation can be identified. The level and position of the scattered photons are recorded as this helps to determine the scattering properties of the sample. This information can be used to provide an indication of the sample structure.
Connected to both the digital mirror and the detector is a computer processor, typically a PC, which has software for analysing the light that is reflected from each element/pixel of the digital mirror and detected signals, thereby to form an image. Because ballistic and scattered photons can be distinguished, the contrast, and hence quality of the infrared transmission images is increased.
In use, a sample is placed in the space between the mirror array and the camera. Alternatively for oral and dental applications either the light source or the detector may be placed inside the oral cavity around the point of interest. Then, the pixels are switched on either in groups or individually. To avoid cross talk, typically adjacent groups are not switched on simultaneously. The light falling on each corresponding camera pixel is then recorded and the next pixel array switched on and its corresponding signal recorded. Thus, only directly transmitted light is detected. After each pair of pixels has been switched on and the signal recorded the image can be displayed. Using collimated beamlets enhances the local effects of scattering centres in the sample, thereby providing images with greater contrast and apparent resolution.
Whilst in the system described above, light is provided from a single high power LED, it could equally be from a laser, such as a laser diode, or from a conventional thermal light source (bulb). The source could be an array of such sources such as an LED micro-array or VCSEL array, provided each beam or group of beams can be mapped onto the detector. In principle, a scanning disc containing an array of holes could be used if it was known exactly which hole was present in front of the source at any one time and hence which detector pixel should be used. Light at around 810nm is preferred for some oral and dental applications. Where high-resolution images of teeth are required, light in the range of llOOnm to 1300nm is preferred. However, other wavelengths could be used to potentially detect other items and to pass through other tissue types.
The imaging method of the present invention offers a significant increase in the contrast of IR images. By investigating the interpretation of the scattered as well as unscattered photons, additional information about the scattering object is provided. For example, scattering will change as a lesion dries out and this rate of change will provide some information on the state of a carious lesion. Thus, the invention provides significantly higher sensitivity to early lesions/tissue changes. The invention makes it possible to image in vivo through the jaws (skin, muscle, gums and bone) to image the developing dentition, which is important in orthodontic and developmental assessments. In particular, the invention makes it possible to image hard dental tissue, in vivo with high image quality. More specifically, the dental tissue that can be imaged includes: 1) carious lesions, including at the early stages 2) the enamel dentine junction, hence image enamel thickness and 3) the root canal system through the gum and bone, offering the possibility of continual assessment during root canal therapy. Other body parts can also be imaged, such as other parts of the head and neck, as well as limbs and possibly parts of the torso. This can all be done without the need for x-rays, thereby offering significant advantages over conventional radiography in terms of health hazards.
A skilled person will appreciate that variations of the disclosed arrangements are possible without departing from the invention. For example, the light source and or detector may be located some distance from the object to be imaged. In this case, suitable means can be used to transmit the beamlets to and/or from the points on either side of the object. For example, the system could be used endoscopically with arrayed fibres delivering and/or receiving the light from a remote source/detector. In addition, although the invention has been described with reference to two-dimensional imaging, separate images taken at different angles could be captured and processed to generate 3-D images. Accordingly the above description of the specific embodiment is made by way of example only and not for the purposes of limitation. It will be clear to the skilled person that minor modifications may be made without significant changes to the operation described.

Claims

Claims
1. A non-scanning medical imager that has a source for providing a plurality of collimated beams of non-ionising radiation and a plurality of correlated detectors, each detector being arranged to receive unscattered light from one or part of one of said collimated beams and scattered light from one or more other beams, the imager further comprising means for using both the unscattered and scattered light to form an image.
2. An imager as claimed in claim 1 wherein the source is a laser, LED or thermal source.
3. An imager as claimed in claim 1 or claim 2 wherein the source is pixelated or be directed onto a device that produces an array of beamlets.
4. An imager as claimed in any of the preceding claims comprising means for switching on simultaneously all or selected groups of the individual beams.
5. An imager as claimed in any of the preceding claims wherein the non-ionising radiation is infrared radiation.
6. An imager as claimed in claim 5 wherein the non-ionising radiation is in the range 810nm to 850nm.
7. An imager as claimed in claim 5 wherein the non-ionising radiation is in the range HOOnm to 1300nm.
8. An imager as claimed in claim 5 wherein the non-ionising radiation is in the near infra-red.
9. An imager as claimed in any of the preceding claims wherein the light is temporally incoherent.
10. An imager as claimed in any of claims 1 to 8 wherein the light is temporally coherent.
11. An imager as claimed in any of the preceding claims comprising one or more filters for preferentially selecting the incident radiation.
12. An imager as claimed in any of the preceding claims comprising means for transmitting radiation from the source to a sample test area.
13. An imager as claimed in claim 12 wherein the means for transmitting comprise an array of fibres.
14. An imager as claimed in any of the preceding claims comprising means for transmitting radiation from a sample area to the detectors.
15. An imager as claimed in claim 14 wherein the means for transmitting comprise an array of fibres.
16. An imager as claimed in any of the preceding claims that is adapted for oral and/or dental use.
17. A method for imaging biological material comprising illumination of a sample using a plurality of collimated beams of non-ionising radiation; detecting radiation that has passed through the sample using a plurality of correlated detectors, each detector being arranged to receive unscattered light from one or part of one of said collimated beams and scattered light from one or more other beams, and using both the unscattered and scattered light to form an image.
18. A method as claimed in claim 17 wherein the sample is illuminated in vivo.
19. A method as claimed in claim 18 wherein the sample is an oral or dental sample such as a tooth.
20. A method as claimed in claim 17 comprising selecting one or more wavelengths for identifying and quantifying the presence of blood and/or small blood vessels in particular regions of an image.
21. A method as claimed in claim 20 comprising using radiation in the wavelength range of 810nm to 850nm.
22. A method as claimed in claim 20 comprising using the identification of blood and/or small blood vessels to identify regions of inflammation.
23. A method of diagnosis of the human or animal body that uses images derived using the system or method of any of the preceding claims.
24. A method as claimed in claim 23 wherein the part of the human or animal body is a tooth.
PCT/GB2008/001085 2007-03-30 2008-03-28 A non-ionising imager WO2008119964A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP08718915A EP2131722A1 (en) 2007-03-30 2008-03-28 A non-ionising imager
US12/594,095 US9084535B2 (en) 2007-03-30 2008-03-28 Non-ionizing imager

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
GB0706155.9 2007-03-30
GB0706155A GB0706155D0 (en) 2007-03-30 2007-03-30 A non-ionising imager

Publications (2)

Publication Number Publication Date
WO2008119964A1 true WO2008119964A1 (en) 2008-10-09
WO2008119964A8 WO2008119964A8 (en) 2009-01-08

Family

ID=38050482

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/GB2008/001085 WO2008119964A1 (en) 2007-03-30 2008-03-28 A non-ionising imager

Country Status (4)

Country Link
US (1) US9084535B2 (en)
EP (1) EP2131722A1 (en)
GB (1) GB0706155D0 (en)
WO (1) WO2008119964A1 (en)

Families Citing this family (63)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11026768B2 (en) 1998-10-08 2021-06-08 Align Technology, Inc. Dental appliance reinforcement
GB0706155D0 (en) * 2007-03-30 2007-05-09 Univ Strathclyde A non-ionising imager
US7878805B2 (en) 2007-05-25 2011-02-01 Align Technology, Inc. Tabbed dental appliance
US8738394B2 (en) 2007-11-08 2014-05-27 Eric E. Kuo Clinical data file
US8108189B2 (en) 2008-03-25 2012-01-31 Align Technologies, Inc. Reconstruction of non-visible part of tooth
US8092215B2 (en) 2008-05-23 2012-01-10 Align Technology, Inc. Smile designer
US9492243B2 (en) 2008-05-23 2016-11-15 Align Technology, Inc. Dental implant positioning
US8172569B2 (en) 2008-06-12 2012-05-08 Align Technology, Inc. Dental appliance
US8152518B2 (en) 2008-10-08 2012-04-10 Align Technology, Inc. Dental positioning appliance having metallic portion
US8292617B2 (en) 2009-03-19 2012-10-23 Align Technology, Inc. Dental wire attachment
US8765031B2 (en) 2009-08-13 2014-07-01 Align Technology, Inc. Method of forming a dental appliance
US9241774B2 (en) 2010-04-30 2016-01-26 Align Technology, Inc. Patterned dental positioning appliance
US9211166B2 (en) 2010-04-30 2015-12-15 Align Technology, Inc. Individualized orthodontic treatment index
US9403238B2 (en) 2011-09-21 2016-08-02 Align Technology, Inc. Laser cutting
US9375300B2 (en) 2012-02-02 2016-06-28 Align Technology, Inc. Identifying forces on a tooth
US9220580B2 (en) 2012-03-01 2015-12-29 Align Technology, Inc. Determining a dental treatment difficulty
US9414897B2 (en) 2012-05-22 2016-08-16 Align Technology, Inc. Adjustment of tooth position in a virtual dental model
WO2015108836A1 (en) * 2014-01-14 2015-07-23 Inventive Medical Devices, Llc Detection of hard and soft tissue mass/density
US10772506B2 (en) 2014-07-07 2020-09-15 Align Technology, Inc. Apparatus for dental confocal imaging
US9675430B2 (en) 2014-08-15 2017-06-13 Align Technology, Inc. Confocal imaging apparatus with curved focal surface
US9610141B2 (en) 2014-09-19 2017-04-04 Align Technology, Inc. Arch expanding appliance
US10449016B2 (en) 2014-09-19 2019-10-22 Align Technology, Inc. Arch adjustment appliance
US9744001B2 (en) 2014-11-13 2017-08-29 Align Technology, Inc. Dental appliance with cavity for an unerupted or erupting tooth
US10504386B2 (en) 2015-01-27 2019-12-10 Align Technology, Inc. Training method and system for oral-cavity-imaging-and-modeling equipment
US10248883B2 (en) 2015-08-20 2019-04-02 Align Technology, Inc. Photograph-based assessment of dental treatments and procedures
US11931222B2 (en) 2015-11-12 2024-03-19 Align Technology, Inc. Dental attachment formation structures
US11554000B2 (en) 2015-11-12 2023-01-17 Align Technology, Inc. Dental attachment formation structure
US11103330B2 (en) 2015-12-09 2021-08-31 Align Technology, Inc. Dental attachment placement structure
US11596502B2 (en) 2015-12-09 2023-03-07 Align Technology, Inc. Dental attachment placement structure
US9554869B1 (en) 2016-01-08 2017-01-31 Eped Inc. Bite tray having fiducial markers for head scan registration and method of use
EP3471599A4 (en) 2016-06-17 2020-01-08 Align Technology, Inc. Intraoral appliances with sensing
EP3471653B1 (en) 2016-06-17 2021-12-22 Align Technology, Inc. Orthodontic appliance performance monitor
CN211433450U (en) 2016-07-27 2020-09-08 阿莱恩技术有限公司 Transillumination adapter sleeve device and transillumination adapter
US10507087B2 (en) 2016-07-27 2019-12-17 Align Technology, Inc. Methods and apparatuses for forming a three-dimensional volumetric model of a subject's teeth
CN109922754B (en) 2016-11-04 2021-10-01 阿莱恩技术有限公司 Method and apparatus for dental images
WO2018102770A1 (en) 2016-12-02 2018-06-07 Align Technology, Inc. Force control, stop mechanism, regulating structure of removable arch adjustment appliance
WO2018102702A1 (en) 2016-12-02 2018-06-07 Align Technology, Inc. Dental appliance features for speech enhancement
US11273011B2 (en) 2016-12-02 2022-03-15 Align Technology, Inc. Palatal expanders and methods of expanding a palate
CN113440273A (en) 2016-12-02 2021-09-28 阿莱恩技术有限公司 Series of palatal expanders and methods and apparatus for forming same
US10548700B2 (en) 2016-12-16 2020-02-04 Align Technology, Inc. Dental appliance etch template
US10456043B2 (en) 2017-01-12 2019-10-29 Align Technology, Inc. Compact confocal dental scanning apparatus
US10779718B2 (en) 2017-02-13 2020-09-22 Align Technology, Inc. Cheek retractor and mobile device holder
US10613515B2 (en) 2017-03-31 2020-04-07 Align Technology, Inc. Orthodontic appliances including at least partially un-erupted teeth and method of forming them
US11045283B2 (en) 2017-06-09 2021-06-29 Align Technology, Inc. Palatal expander with skeletal anchorage devices
WO2018232299A1 (en) 2017-06-16 2018-12-20 Align Technology, Inc. Automatic detection of tooth type and eruption status
WO2019005808A1 (en) 2017-06-26 2019-01-03 Align Technology, Inc. Biosensor performance indicator for intraoral appliances
US10885521B2 (en) 2017-07-17 2021-01-05 Align Technology, Inc. Method and apparatuses for interactive ordering of dental aligners
WO2019018784A1 (en) 2017-07-21 2019-01-24 Align Technology, Inc. Palatal contour anchorage
CN110996842B (en) 2017-07-27 2022-10-14 阿莱恩技术有限公司 Tooth staining, transparency and glazing
US10517482B2 (en) 2017-07-27 2019-12-31 Align Technology, Inc. Optical coherence tomography for orthodontic aligners
US11116605B2 (en) 2017-08-15 2021-09-14 Align Technology, Inc. Buccal corridor assessment and computation
WO2019036677A1 (en) 2017-08-17 2019-02-21 Align Technology, Inc. Dental appliance compliance monitoring
US10813720B2 (en) 2017-10-05 2020-10-27 Align Technology, Inc. Interproximal reduction templates
WO2019084326A1 (en) 2017-10-27 2019-05-02 Align Technology, Inc. Alternative bite adjustment structures
CN116602778A (en) 2017-10-31 2023-08-18 阿莱恩技术有限公司 Dental appliance with selective bite loading and controlled tip staggering
CN115252177A (en) 2017-11-01 2022-11-01 阿莱恩技术有限公司 Automated therapy planning
WO2019100022A1 (en) 2017-11-17 2019-05-23 Align Technology, Inc. Orthodontic retainers
US11219506B2 (en) 2017-11-30 2022-01-11 Align Technology, Inc. Sensors for monitoring oral appliances
US11432908B2 (en) 2017-12-15 2022-09-06 Align Technology, Inc. Closed loop adaptive orthodontic treatment methods and apparatuses
US10980613B2 (en) 2017-12-29 2021-04-20 Align Technology, Inc. Augmented reality enhancements for dental practitioners
CA3086553A1 (en) 2018-01-26 2019-08-01 Align Technology, Inc. Diagnostic intraoral scanning and tracking
US11937991B2 (en) 2018-03-27 2024-03-26 Align Technology, Inc. Dental attachment placement structure
CN116211501A (en) 2018-04-11 2023-06-06 阿莱恩技术有限公司 Palate expander, palate expander device and system, and method for forming palate expander

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6243601B1 (en) * 1998-09-18 2001-06-05 Abund Ottokar Wist Transillumination imaging instrumentation with scattered light discrimination
WO2003021329A2 (en) * 2001-08-31 2003-03-13 Smith & Nephew, Inc. Solid-state light source
WO2003069391A1 (en) * 2002-02-14 2003-08-21 Carl Zeiss Microelectronic Systems Gmbh Device for confocal, optical microanalysis
JP2006133499A (en) * 2004-11-05 2006-05-25 Shimadzu Corp Confocal scanner and confocal microscope

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS60181638A (en) * 1984-02-29 1985-09-17 Toshiba Corp Photography method of radiation image
US4945239A (en) * 1989-03-29 1990-07-31 Center For Innovative Technology Early detection of breast cancer using transillumination
US6485413B1 (en) * 1991-04-29 2002-11-26 The General Hospital Corporation Methods and apparatus for forward-directed optical scanning instruments
US5570182A (en) * 1994-05-27 1996-10-29 Regents Of The University Of California Method for detection of dental caries and periodontal disease using optical imaging
GB9703156D0 (en) * 1997-02-15 1997-04-02 Univ Strathclyde Optical element
US7338168B2 (en) * 2001-07-06 2008-03-04 Palantyr Research, Llc Particle analyzing system and methodology
WO2005013843A2 (en) 2003-08-08 2005-02-17 The Regents Of The Univeristy Of California Near-infrared transillumination for the imaging of early dental decay
US7796243B2 (en) * 2004-06-09 2010-09-14 National Research Council Of Canada Detection and monitoring of changes in mineralized tissues or calcified deposits by optical coherence tomography and Raman spectroscopy
WO2006039091A2 (en) * 2004-09-10 2006-04-13 The General Hospital Corporation System and method for optical coherence imaging
US20080062429A1 (en) * 2006-09-12 2008-03-13 Rongguang Liang Low coherence dental oct imaging
GB0706155D0 (en) * 2007-03-30 2007-05-09 Univ Strathclyde A non-ionising imager

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6243601B1 (en) * 1998-09-18 2001-06-05 Abund Ottokar Wist Transillumination imaging instrumentation with scattered light discrimination
WO2003021329A2 (en) * 2001-08-31 2003-03-13 Smith & Nephew, Inc. Solid-state light source
WO2003069391A1 (en) * 2002-02-14 2003-08-21 Carl Zeiss Microelectronic Systems Gmbh Device for confocal, optical microanalysis
JP2006133499A (en) * 2004-11-05 2006-05-25 Shimadzu Corp Confocal scanner and confocal microscope

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
JONES G C ET AL: "Transillumination of interproximal caries lesions with 830-nm light", PROCEEDINGS OF THE SPIE, SPIE, BELLINGHAM, VA, vol. 5313, no. 1, 1 January 2004 (2004-01-01), pages 17 - 22, XP007905036, ISSN: 0277-786X *
See also references of EP2131722A1 *

Also Published As

Publication number Publication date
US20100137722A1 (en) 2010-06-03
US9084535B2 (en) 2015-07-21
WO2008119964A8 (en) 2009-01-08
GB0706155D0 (en) 2007-05-09
EP2131722A1 (en) 2009-12-16

Similar Documents

Publication Publication Date Title
US9084535B2 (en) Non-ionizing imager
Simon et al. Near‐IR transillumination and reflectance imaging at 1,300 nm and 1,500–1,700 nm for in vivo caries detection
US10251558B2 (en) Method and apparatus for measuring and displaying dental plaque, gingiva, and alveolar bone
US5818587A (en) Image measuring apparatus
CN101426420B (en) Optical detection of dental caries
CN101528116B (en) Apparatus for caries detection
CN101553161B (en) Apparatus for caries detection
DK2668904T3 (en) Spectral filter for an intraoral imaging system
US7965392B2 (en) Optical coherence tomography device and measuring head
JP6113655B2 (en) Optically integrated handpiece for photothermal radiation and luminescence measurements
US8798699B2 (en) Spectroscopic detection of malaria via the eye
Angelino et al. Near-infrared imaging for detecting caries and structural deformities in teeth
CN101563021A (en) Apparatus for dental optical coherence tomography imaging
Ozkan et al. Clinical evaluation of near-infrared light transillumination in approximal dentin caries detection
JP2009165831A (en) Intra-oral imaging apparatus for diagnostic and cosmetic imaging
Bansode et al. Diagnosing dental caries: An insight
Lee et al. In vitro near-infrared imaging of occlusal dental caries using a germanium-enhanced CMOS camera
Solanki et al. Advanced diagnostic aids in dental caries–a review
US20120122052A1 (en) Medical, in Particular Dental, Diagnostic Device Having Image Capture Means
Zhou et al. Near‐infrared multispectral endoscopic imaging of deep artificial interproximal lesions in extracted teeth
KR101904830B1 (en) Optical imaging system for oral cavity
JP4109132B2 (en) Fluorescence determination device
EP0984717A1 (en) Non-invasive diagnostic method and apparatus
Al Saffan Current Approaches to Diagnosis of Early Proximal Carious Lesion: A Literature Review
JP4109133B2 (en) Fluorescence determination device

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 08718915

Country of ref document: EP

Kind code of ref document: A1

WWE Wipo information: entry into national phase

Ref document number: 2008718915

Country of ref document: EP

WWE Wipo information: entry into national phase

Ref document number: 12594095

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: DE