WO2015121115A1 - Dispositif photonique ayant une pointe lisse et une sortie de lumière améliorée - Google Patents

Dispositif photonique ayant une pointe lisse et une sortie de lumière améliorée Download PDF

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Publication number
WO2015121115A1
WO2015121115A1 PCT/EP2015/052228 EP2015052228W WO2015121115A1 WO 2015121115 A1 WO2015121115 A1 WO 2015121115A1 EP 2015052228 W EP2015052228 W EP 2015052228W WO 2015121115 A1 WO2015121115 A1 WO 2015121115A1
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Prior art keywords
optical fiber
front surface
channel
shaft
μιη
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PCT/EP2015/052228
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English (en)
Inventor
Christian Reich
Gerhardus Wilhelmus Lucassen
Klaas Cornelis Jan Wijbrans
Torre Michelle BYDLON
Waltherus Cornells Jozef BIERHOFF
Bernardus Hendrikus Wilhelmus Hendriks
Stephan Voss
Axel Winkel
Marjolein Van Der Voort
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Koninklijke Philips N.V.
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Publication of WO2015121115A1 publication Critical patent/WO2015121115A1/fr

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    • 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
    • A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6848—Needles
    • 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
    • A61B2562/12—Manufacturing methods specially adapted for producing sensors for in-vivo measurements
    • 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
    • A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy

Definitions

  • the invention generally relates to a device and a system including the same. Particularly, the invention relates to a device with optical fibers.
  • tissue sensing at the tip of the device may be required.
  • Current needles often do not have such tissue feedback possibilities.
  • elongated interventional devices have been reported with optical fibers integrated into the device which provide feedback from the tissue at the tip of the device. Such devices allow for fine-guidance towards small volumes of suspicious tissue, in particular for tissue which does not show sufficient contrast in imaging.
  • these devices employ diffuse reflectance spectroscopy (DRS).
  • DRS diffuse reflectance spectroscopy
  • a photonic needle for example a biopsy device including at least one optical fiber for emitting and receiving light, may determine tissue type by sending light with a broadband spectrum into the body, measuring the reflected spectrum and determining the type of tissue by the application of an algorithm on this spectrum.
  • a needle with straight cut fibers was used.
  • the shape of the light beam is advantageous, it has the severe disadvantage of having pockets in which tissue stays behind thus polluting the measurement.
  • Slanted fiber ends along the sharp bevel angle of the cannula would ensure smooth, unobstructed puncturing of the needle, however, coupling the light output with straight cut fibers is found to be more efficient compared to the light coupling with slanted fiber ends.
  • the use of a beveled fiber changes the direction of the light out of the needle reducing the light output significantly due to internal reflection, with even no output (total internal reflection).
  • US 2011/0251494 describes a needle device, wherein optical fibers are integrated in the device such that the fiber distal ends are located in the slanted bevel of the needle device, with the fiber distal end surfaces being polished.
  • the general problem is how to integrate optical fibers into the elongated tube of the interventional device in a way which optimizes the coupling of light into tissue for illumination and detection. Furthermore, the solution should be cost effective since comparable commercial needles without tissue sensing are low cost disposable devices.
  • the problem may be that the slanted edge of the fiber acts as a prism. This means that the light is deflected downwards, according to the refractory index of the different materials. Because the light output of the fiber is a cone at a certain moment part of the light will be reflected internally, and if the angle gets sharp enough all light will be reflected internally. In the case of the photonic needle when inserted to the body, the refractory index in the body is approximately 1.33 (refractory index of water). The refractory index of the core of a silica/silica fiber is approximately 1.52. At a bevel angle of 15°, it then follows that all light is reflected internally. Into air, the situation is even worse because the refractory index of air is approximately 1. So, also with a bevel angle of 30° in air almost no light exits from the needle, thus making calibration of the needle before the procedure difficult.
  • embodiments in accordance with the invention propose designs to ensure a smooth needle insertion where the optical fiber ends are adapted to the needle tip design, with the requirement that the light loss is minimized to an acceptable level.
  • the proposed embodiments focus on optimizing the light coupling into tissue. Accordingly, the light output from the slanted fiber ends is enhanced by increasing the surface roughness of the tip of the optical fiber. Thereby, the probability for light being reflected downwards at the slanted interface due to a mismatch in refractive index is reduced by the presence of an interface as defined in accordance with the invention.
  • a device comprises a shaft and an optical fiber accommodated within the shaft, wherein the distal surface of the shaft is slanted, i.e. forms a bevel surface, and wherein the distal end of the optical fiber is correspondingly slanted and arranged so as to be co-planar to the bevel surface of the shaft.
  • the slanted front surface of the optical fiber is roughened.
  • the device includes a longitudinal main axis, usually the center axis of a rotationally symmetrical shaft. Further, the tip portion of the device is cut at an angle to the main axis forming the bevel. The pointed tip of the bevel is directed to the 'front' of the needle. As a result, looking from the 'side', i.e. 'laterally', it is possible to recognize the angle between the bevel and the main axis.
  • a 'bevel' is a geometrical structure allowing for introducing the device, for example a needle into tissue.
  • a shaft of the device includes a circular cross section. The distal end of the shaft is cut such that an oval surface is formed, which is inclined relative to the longitudinal axis of the shaft.
  • the bevel forms a pointed tip at the most distal end of the device. It should be noted that the bevel might form an acute angle with the shaft, such that the device includes a pointed tip. The acute angle might be between 20° and 40°, preferably 32°.
  • the end surface of an optical fiber at the opening in the bevel may have a circular shape or a more or less oval shape in case of a substantially circular cross section of the fiber.
  • the shape of the end surface of the fiber will be effected and therefore also the direction of the emitted or received light.
  • the distance between the fiber ends may be greater than the diameter of the shaft.
  • the distance may be more than 1.1 times greater than the diameter.
  • the distance may be more than 1.25 times greater than the diameter.
  • the distance may be more than 1.5 times greater than the diameter.
  • the distance between the fiber ends should be as great as possible. Such distances are measured from the central axis of one of the fibers to the central axis of the other one of the fibers.
  • a device may comprise an elongated shaft including a bevel surface, wherein a plane is defined by the bevel surface.
  • the shaft further includes a channel extending through the shaft parallel to the longitudinal axis, the channel forming an opening in the bevel surface, and an optical fiber with a front surface, wherein the optical fiber is arranged within the channel of the shaft so that the front surface is located in the plane defined by the bevel surface, the front surface having the size and shape of the opening formed in the bevel surface, so that a smooth distal surface without any gaps is formed at the distal end by the bevel surface and the front surface when the optical fiber is accommodated within the channel.
  • the front surface of the optical fiber is treated so as to have a predetermined roughness.
  • a tool may be utilized for treating the front surface of the optical fiber, which tool comprises a roughness, i.e. a fineness of grind of at least 15 ⁇ .
  • the roughness may be between 20 ⁇ and 60 ⁇ or between 25 ⁇ and 40 ⁇ .
  • the front surface of the optical fiber will be provided with a corresponding roughness, when treated with such a tool.
  • a treatment of the front surface of the optical fiber with a tool having a roughness of 30 ⁇ will result in a roughness of the front surface of approximately 30 ⁇ .
  • the front surface of the optical fiber may be treated with a linear, circular, oval or 8-shape grinding movement, or even with a chaotic grinding movement.
  • the front surface of the optical fiber may be treated by sand blasting. It will be understood that the achieved roughness on a surface depends on the size of the used sand grain.
  • the elongated shaft comprises more than one channel, wherein a first opening formed in the bevel surface by a first channel is located more proximally than the a second opening formed in the bevel surface by a second channel, and wherein the needle comprises more than one optical fiber each arranged within one of the channels.
  • the elongated shaft may comprise three channels each forming an opening in the bevel surface, wherein a first opening is located proximally, a second opening is located in the proximity of the first opening, and a third opening is located distally, and wherein the needle comprises at least one optical fibers arranged in the channels of the elongated shaft.
  • a reflective coating may be provided at a channel wall of the channel. It is noted that the coating may be provided in all channels, but also in only one or two of the channels. Furthermore, it may be advantageous to provide the coating only in a section of a channel.
  • a system including the above described device as well as a console including a light source, a light detector and a processing unit for processing the signals provided by the light detector, wherein one of the light source and the light detector may provide wavelength selectivity.
  • the light source may be one of a laser, a light-emitting diode or a filtered light source
  • the console may further comprise one of a fiber switch, a beam splitter or a dichroic beam combiner.
  • the device may be adapted to perform at least one out of the group consisting of diffuse reflectance spectroscopy, diffuse optical tomography, differential path length spectroscopy, and Raman spectroscopy.
  • the device may further comprise a channel for injecting or extracting a fluid.
  • the device may be an injection needle for injecting for example a local narcotic.
  • a channel may be an additional channel formed in the shaft or in an insert, and extending through that insert in a longitudinal direction, but may also be formed in the wall of the shaft or between the insert and the shaft or between the shaft and an additional outer tubular member.
  • the device may further comprise a tissue retraction channel, wherein a suction device may apply vacuum to the channel for retracting a sample of tissue.
  • a suction device may apply vacuum to the channel for retracting a sample of tissue.
  • the channel in which an insert is accommodated within the hollow shaft may be used for retracting a sample, after removing the insert.
  • the channel may be formed in the shaft or an insert between optical fibers which are preferably arranged as much as possible at opposite sides of the shaft or insert.
  • a method for producing a device as described comprising the steps of providing a shaft with a channel formed parallel to a longitudinal axis of the shaft, and with a bevel surface formed with an acute angle relative to the longitudinal axis, providing an optical fiber with a front surface formed with the same acute angle relative to the longitudinal axis as the bevel surface, positioning the optical fiber in the channel so that the front surface of the optical fiber together with the bevel surface of the shaft form a smooth distal surface of the needle, and treating the front surface of the optical fiber so as to provide a predetermined roughness on the front surface of the optical fiber.
  • Figure 1 is an illustration of light reflection within an optical fiber.
  • Figure 2 shows an embodiment of a device with rough fiber ends.
  • Figure 3 illustrates distal surfaces of embodiments of devices.
  • Figure 4 shows embodiments with different fiber arrangements.
  • Figure 5 illustrates a device according to another embodiment.
  • Figure 6 shows a system including a device and a console.
  • Figure 7 shows a log plot of absorption coefficient of blood, water and fat.
  • Figure 8 shows fluorescence curves for collagen, elastin, NADH and FAD.
  • Figure 9 is a flow chart illustrating steps of a method according to an embodiment.
  • Figure 1 is a sectional view of a distal end portion of an optical fiber.
  • the fiber includes a core 20, a cladding 22 and a buffer 24.
  • light is internally reflected for rays with an angle ⁇ ⁇ 90-9c where 9c is the critical angle at which the rays still undergo total internal reflection at the core cladding interface.
  • Light coupling in or out from the fiber occurs for rays with angles ⁇ ⁇ 9max.
  • Internal reflection at a slanted fiber interface towards cladding and buffer causes reduced light output coupling for illumination and in coupling for detection since the angle ⁇ for these rays will be ⁇ > 90- ⁇ c and do not undergo total reflection but is transmitted to the buffer and can be absorbed and scattered by the buffer material.
  • a needle tip can be shaped in a way so that it does not contain any undesired ridges, has a smooth shape to minimize pockets by adjusting the optical insert with a slanted angle matching to that of the needle bevel angle. This can be achieved by polishing/grinding the entire needle tip including the optical fibers.
  • the reflection at the slanted front surface 45 of the fiber 40 may redirect a significant part of the light into the cladding 22 and buffer material of the fibers where it may be lost due to absorption.
  • the light hitting the sides of the lumen may be re-directed outwards and upwards.
  • the undesired internal reflection at the slanted fiber interface may be reduced by roughening the surface 45 of the polished fiber tip end.
  • the effective light output at the slanted fiber/air interface is enhanced for roughly polished fibers (average surface roughness of 30 ⁇ ) as compared to fine-polished fibers (roughness ⁇ ), see figure 2.
  • the signal is particularly enhanced in the wavelength range from 400nm to 500nm.
  • the roughening can be done in a variety of ways.
  • the polishing can be done with a polishing foil with the desired surface roughness.
  • the polishing can be applied by moving the foil continuously in an ,,8-shape" above the needle tip surface, instead of only a linear or circular direction.
  • a distal surface of a device is illustrated, which includes a bevel surface 30 of the shaft 10, a bevel surface 35 of an insert and slanted front surfaces 45 of optical fibers, and which is polished in a linear manner by a foil.
  • the needle tip surface could be also fine polished to achieve a very smooth surface (without any macroscopic gaps), and then roughened up again by sandblasting using grains with a size corresponding to the desired end surface roughness.
  • An example of a distal surface treated in that way is illustrated on the right side of figure 3.
  • FIG 4 embodiments are shown, which differ with respect to the arrangement of the front surfaces of the fibers 40 in the bevel surface 30 of the shaft 10, wherein the bevel surface 30 is formed by a combination of a bevel surface of an insert 30 and a co-planar bevel surface of an outer tubular shaft 10. This can be seen in particular on the right side in the figure, showing front views of the embodiments.
  • the shaft 10 comprises three channels each forming an opening in the bevel surface 30, wherein a first opening is located proximally, a second opening is located in the proximity of the first opening, i.e. beside the first opening, and a third opening is located distally, and wherein the needle comprises two optical fibers 40 arranged in two of the three channels of the elongated shaft, respectively.
  • the optical fiber which ends distally is used as a source fiber, i.e. for emitting light out of the device and into tissue.
  • the arrangement of the optical fibers 40 at the needle tip can affect the light output efficiency.
  • the signal output may differ in case the insert 35 and/or the inner surface of the shaft 30 reflect light differently (e.g. due to different surface roughness, etc.).
  • the inner surface of the shaft may be more smooth (and may have better light reflection) than the insert at the tip. This becomes relevant for the fraction of light which is reflected from the slanted fiber tip back into the cladding/buffer, and then hits the metal which is holding the fiber. The more reflective the metal surface is, the higher the probability that part of this light is being back-reflected out of the optical fiber.
  • the tip angle a and the distance between the fiber tips is the same for both designs, the light intensity output is different due to the positioning of the fiber tip ends next to either the inner surface of the shaft or the insert.
  • the optical fiber 40 may comprise a distal tip portion 50 and a proximal portion with a contact surface 55 between the distal tip portion and the proximal portion, wherein the distal tip portion may be made from a plastic material with wide-band optical transmission and low attenuation like a Teflon based plastic, for example CYTOP that is used in Gigabit optical fibers.
  • the plastic material may be different to the material of the proximal portion of the optical fiber, so that light refraction occurs at the contact surface.
  • the contact surface may be straight-cut being perpendicular to the longitudinal axis of the shaft.
  • the loss of light from the straight-cut fiber into a CYTOP plug as distal tip portion is minimal, with a refractory index of the material of the distal tip portion nl of 1.34 and a refractory index of the material of the proximal portion n2 of 1.52, only 0.6% of the light is lost through reflection.
  • the deflection of the light is determined by nl of 1.33 and n2 of 1.34, resulting in a change in direction of only 1.7 degrees.
  • nl 1.33
  • n2 1.34
  • the contact surface 55 between the proximal portion of the fiber 40 and the distal tip portion 50 is slanted. This may additionally be used to direct the light in a specific direction.
  • the direction of the beam can be steered upwards or downwards (or even sideways if that proves advantages).
  • the area where the cones of the two fibers cross can be adjusted.
  • the exact position of the straight-cut fiber end becomes less critical and especially if a manufacturing process is used where first the fiber is inserted into the shaft 10 or an insert 35 and then the distal tip portions in form of plugs are molded into the resulting cavities.
  • the plug can compensate for tolerances in the exact end position of the fibers.
  • the fibers 40 of the interventional device are connected to an optical console 60.
  • the optical fibers can be understood as light guides or optical waveguides.
  • the console 60 comprises a light source 64 in the form of a halogen broadband light source with an embedded shutter, and an optical detector 66.
  • the optical detector 66 can resolve light with a wavelength substantially in the visible and infrared regions of the wavelength spectrum, such as from 400 nm to 1700 nm.
  • the combination of light source 64 and detector 66 allows for diffuse reflectance measurements. For a detailed discussion on diffuse reflectance measurements see R. Nachabe, B.H.W. Hendriks, A.E.
  • the console is couple to an imaging modality capable of imaging the interior of the body, for instance when the biopsy is taken under image guidance.
  • an imaging modality capable of imaging the interior of the body
  • the in- vivo information of the optical biopsy needle, the information of the pathology of the biopsy as well as the location where the biopsy was taken may be brought together for advanced pathology.
  • optical methods can be envisioned like diffuse optical tomography by employing a plurality of optical fibers, differential path length spectroscopy, fluorescence and Raman spectroscopy to extract tissue properties.
  • a suction device 70 may be connected to a proximal end of the biopsy device, such that underpressure or a vacuum can be applied through the biopsy device to the distal end of the same.
  • the device 80 may be connected to the console 60 by means of a wire or wireless, for interchanging information like control commands or data representing pathological aspects of an inspected tissue sample.
  • the device 80 may be a digital pathology systems consisting of an optical scanner and an image management system to enable digitizing, storage, retrieval, and processing of tissue staining images, reading the
  • the data set from the photonic biopsy device may be either presented next to the histopathology image or the two data sets may be fused in the image, characterized and recognizable by a certain coloring pattern of the image.
  • the oxygenation level measured in- vivo could be added as a red color, where deep red means low oxygenation and bright red would mean high oxygenation level.
  • molecular spatial distributions from FTIR or Raman could be added as a color coded mapping to the pathology slide of specific molecules.
  • the tissue sample which may firstly be subjected to an in- vivo tissue inspection, i.e. an inspection within a living body, and which may secondly subjected to an ex-vivo tissue inspection by means of the device 80, may be situated in the container 90.
  • tissue inspection i.e. an inspection within a living body
  • ex-vivo tissue inspection by means of the device 80
  • Molecular diagnostics can also be performed on the tissue biopsy (e.g. sequencing or PCR), or part of the biopsy.
  • a processor transforms the measured spectrum into physiological parameters that are indicative for the tissue state and a monitor 68 may be used to visualize the results.
  • a computer program executable on the processor may be provided on a suitable medium such as an optical storage medium or a solid-state medium supplied together with or as part of the processor, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems.
  • the console must be capable of providing excitation light to at least one source fiber while detecting tissue-generated fluorescence through one or more detection fibers.
  • the excitation light source may be a laser (e.g. a semiconductor laser), a light-emitting diode (LED) or a filtered light source, such as a filtered mercury lamp.
  • the wavelengths emitted by the excitation light source are shorter than the range of wavelengths of the fluorescence that is to be detected. It is preferable to filter out the excitation light using a detection filter in order to avoid possible overload of the detector by the excitation light.
  • a wavelength-selective detector e.g. a spectrometer, is required when multiple fluorescent entities are present that need to be distinguished from each other.
  • the excitation light for measuring fluorescence may be provided to the same source fiber as the light for diffuse reflectance. This may be accomplished by, e.g., using a fiber switch, or a beam splitter or dichroic beam combiner with focusing optics. Alternatively, separate fibers may be used for providing fluorescence excitation light and light for diffuse reflectance measurements.
  • the acquired spectra may be fitted using a custom made Matlab 7.9.0 (Mathworks, Natick, MA) algorithm.
  • Matlab 7.9.0 Matlab 7.9.0
  • a widely accepted analytical model was implemented, namely the model introduced by the reference T. J.Farrel,
  • the input arguments for the model of this reference are the absorption coefficient ⁇ 3 ( ⁇ ), the reduced scattering coefficient ⁇ 5 ' ( ⁇ ) and the center-to-center distance between the emitting and collecting fibers at the tip of the probe.
  • the parameter a corresponds to the reduced scattering amplitude at this specific wavelength.
  • ⁇ 5 (1) a (p MR ( ) + (1 - p MR ) ( ) ) [cm- 1 ] (Eq. 1)
  • the reduced scattering coefficient is expressed as the sum of Mie and Rayleigh scattering where p MR is the Mie-to-total reduced scattering fraction.
  • the reduced scattering slope of the Mie scattering is denoted b and is related to the particle size.
  • the total light absorption coefficient ⁇ ⁇ ( ⁇ ) can be computed as products of the extinction coefficients and volume fraction of the absorbers (see Figure 8)
  • ⁇ ⁇ 00 ⁇ (A) corresponds to the absorption by blood
  • ⁇ TM 1 (A) corresponds to absorption by water and lipid together in the probed volume.
  • the factor C is a wavelength dependent correction factor that accounts for the effect of pigment packaging and alters for the shape of the absorption spectrum. This effect can be explained by the fact that blood in tissue is confined to a very small fraction of the overall volume, namely blood vessels. Red blood cells near the center of the vessel therefore absorb less light than those at the periphery. Effectively, when distributed homogeneously within the tissue, fewer red blood cells would produce the same absorption as the actual number of red blood cells distributed in discrete vessels.
  • the correction factor can be describ
  • R denotes the average vessel radius expressed in cm.
  • the absorption coefficient related to blood is given by
  • aBL [Hb0 2 ]/ ([Hb0 2 ] + [Hb]) and is commonly known as the blood oxygen saturation.
  • optical tissue properties may be derived such as the scattering coefficient and absorption coefficient of different tissue chromophores: e.g. hemoglobin, oxygenated haemoglobin, water, fat etc. These properties are different between normal healthy tissue and diseased (cancerous) tissue.
  • tissue chromophores e.g. hemoglobin, oxygenated haemoglobin, water, fat etc.
  • the main absorbing constituents in normal tissue dominating the absorption in the visible and near-infrared range are blood (i.e. hemoglobin), water and fat.
  • blood i.e. hemoglobin
  • water and fat the absorption coefficient of these chromophores as a function of the wavelength are presented. Note that blood dominates the absorption in the visible range, while water and fat dominate in the near infrared range.
  • the total absorption coefficient is a linear combination of the absorption coefficients of for instance blood, water and fat (hence for each component the value of that shown in figure 7 multiplied by its volume fraction).
  • Another way to discriminate differences in spectra is by making use of a principal components analysis. This method allows classification of differences in spectra and thus allows discrimination between tissues. Apart from diffuse reflectance also fluorescence may be measured. Then for instance parameters like collagen, elastin, NADH and FAD could be measured too (see figure 8). Especially, the ratio NADH/FAD, which is called the optical redox parameter, is of interest because it is an indicator for the metabolic state of the tissue, as described in Zhang Q., et al. "Turbidity-free fluorescence spectroscopy of biological tissue", Opt. Lett., 2000 25(19), p. 1451-1453, which is changed in cancer cells and assumed to change upon effective treatment of cancer cells.
  • optical biopsy device It is also possible to detect the response of the body to exogenous fluorophores that can be detected by the optical biopsy device. Furthermore, these could also be linked to measurements of the exogenous fluorophores by imaging modalities like optical
  • Fig. 9 illustrates the principle of the steps performed in accordance with an embodiment described herein. It will be understood that the steps described, are major steps, wherein these major steps might be differentiated or divided into several sub-steps. Furthermore, there might be also sub-steps between these major steps.
  • a shaft 10 is provided with a channel formed parallel to a longitudinal axis of the shaft, and with a bevel surface 30 formed with an acute angle relative to the longitudinal axis.
  • step S2 an optical fiber is provided with a front surface formed with the same acute angle relative to the longitudinal axis as the bevel surface of the shaft.
  • step S3 the optical fiber is positioned in the channel so that the front surface of the optical fiber together with the bevel surface of the shaft form a smooth distal surface of the needle.
  • step S4 the front surface of the optical fiber is treated so as to provide a predetermined roughness on the front surface of the optical fiber.

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Abstract

En général, un dispositif selon l'invention comprend une tige et une fibre optique logée à l'intérieur de la tige, la surface distale de la tige étant inclinée, c'est-à-dire formant une surface biseautée, et l'extrémité distale de la fibre optique étant inclinée de manière correspondante et placée de façon à être coplanaire à la surface biseautée de la tige. En particulier, la surface avant inclinée de la fibre optique est rendue rugueuse.
PCT/EP2015/052228 2014-02-14 2015-02-04 Dispositif photonique ayant une pointe lisse et une sortie de lumière améliorée WO2015121115A1 (fr)

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