Patent Application
20160051832
The present invention relates to a medical device, its preparation method and applications thereof.
Photodynamic therapy (PDT) is a non-thermal technique which can be used to produce localised tissue necrosis. This requires activating a pre-administered photosensitizer with light of a specific wavelength to form a cytotoxic species from molecular oxygen (mostly singlet oxygen). For a photodynamic reaction to occur, the photosensitising agent, activating light and oxygen must be present in sufficient amounts.
The therapeutic effect of photodynamic therapy depends on a combination of parameters that include drug dose, drug-light interval, oxygen and light fluence rate. It also varies according to the wavelength distribution of the light source. Finally, a homogeneous and reproducible fluence rate delivery during clinical PDT is determinant in preventing under- or overtreatment. In Dermatology, topical PDT has been carried out with a wide variety of light sources delivering a broad range of light doses. Irradiance is usually limited to less than 100 mW·cm−2.
Light-emitting diodes (LEDs) are now considered as an appropriate light source for PDT. Indeed, LEDs have a relatively narrow bandwidth (usually 20 to 30 nm) and are available in a wide range of wavelengths. LED systems for Methyl aminolevulinate PDT (MAL-PDT) such as Aktilite® CL 16 and Aktilite® CL 128 (Metvix, Galderma) are now mainly used. The Aktilite® CL 16 treats areas of skin measuring 40×50 mm whereas the Aktilite® CL 128 treats larger areas (80×180 mm) (
Also a homogeneous and reproducible fluence delivery rate during clinical photodynamic therapy plays a determinant role in preventing under- or over-treatment. Photodynamic therapy applied in Dermatology has been carried out with a wide variety of light sources delivering a broad range of more or less adapted light doses. Due to the complexity of human anatomy, such as the human face and also vulval, and perianal areas, these light sources do not in fact deliver a uniform light distribution to the skin. Therefore, the development of flexible light sources considerably improves the homogeneity of light delivery. The integration of plastic optical fibres into textile structures offers an interesting alternative to rigid light emitters.
In dermatology, the clinical use of 5-aminolaevulinic acid (ALA) induced protoporphyrin IX (PPIX) for photodynamic therapy is proposed for non-melanoma skin cancer treatment. However, this treatment is painful limiting the suitability of photodynamic therapy as a treatment of first choice. Patients report a burning or tingling sensation that sometimes leads to need for local anesthesia or termination of therapy. Especially treating extensive field cancerization with actinic keratosis in the face and scalp region is painful for the patient.
One way to reduce the pain consists in light dose fractionation. Irradiation is interrupted at a particular point for a period of time. There is therefore a succession of illumination periods and of rest periods. Besides, light fractionation to increases the efficacy: light fractionation produces more necrosis than with the same light dose delivered without rest periods.
Conventional light sources necessary for photodynamic therapy are expensive. Therefore an inactive or rest period is a waste of medical means.
Consequently the use of PDT has largely been limited to hospital outpatient services where costs can be high and the service inconvenient for the patient.
New concepts in illumination, such as ambulatory PDT or daylight illumination might contribute to the further acceptance of this method.
Additionally, actinic keratosis (AK) are scaly or crusty growths (lesions) caused by damage from the sun's ultraviolet rays (UVR). Actinic Keratosis is also known as solar keratosis. Untreated actinic keratosis can advance to squamous cell carcinoma (SCC), the second most common form of skin cancer. Treatment options include ablative (destructive) therapies such as cryosurgery, curettage with electrosurgery, and photodynamic therapy. Topical photodynamic therapy for actinic keratosis is now a well established treatment modality, with two drugs registered for this indication. In the last years, new formulations have been developed, which promise a further improvement of actinic keratosis treatment. Photodynamic therapy is well tolerated, has excellent cosmetic results, and has reported cure rates between 69 and 93%, with fewer side effects compared to the other treatment options. Presently, a flat LED panel is used as light source.
A conventional protocol using Metvix® (methyl aminolevulinate) consists in having Metvix® specifically absorbed into the altered skin cells of these lesions. Metvix® causes compounds called porphyrins to accumulate and be absorbed selectively by the actinic keratosis. Metvix® is applied to the lesions to be treated. The lesion is covered with a dressing. There is a 3 hour waiting period for the Metvix® cream to be absorbed. After 3 hours, Metvix® is washed off and immediately illuminated with a red light, the intensity and time exposed to red light depends on the type of lesions that are treated. Light exposure can last between 8-20 minutes. The illumination is not homogeneous since a LED panel is used.
The size and the design of the led panel are not appropriate for bald scalps. Since the treatment is performed in a short period of time, the treatment is usually very painful.
US 2006/0257095 discloses a light diffuser for photodynamic therapy comprising a flat flexible support and a plurality of light-emitting elements affixed thereto. Each light-emitting element of the light diffuser further comprises a light-supplying optical fiber, said optical fiber not being a woven or integral part of said flexible support. To each optical fiber there is associated exactly one light-emitting element that comprises at least one output zone formed by a local curvature of the optical fiber by either a fixation stitch or at least one loop. The light diffusers are flexible, and may be used on complex body surfaces.
However, in a publication in the Journal of Biomedical Optics 12 3, 034024 May/June 2007, the inventors stated that a power setting of 100 mW increases the temperature of the textile diffuser surface of up to 27° C., and a power of 1 W heated the textile diffuser from 22° C. to more than 30° C. in less than 1 min, and induced a mean temperature on the surface of 36° C. and maximum values above 40° C. after 5 min. Furthermore, illumination is not homogeneous as shown on a figure representing a 3-D image and a brightness distribution histogram of the calculated luminous textile surface. The emission of each point can easily be recognized on a figure hereafter showing the light emitted by the above light diffuser. The textile diffuser achieved an irradiance of 3.6 mW/cm2. Development of this light diffuser was therefore stopped.
One challenge in order to ensure the development of such treatment is to guarantee a uniform light illumination of the skin due to the complexity of the human anatomy and an important irradiance while avoiding excessive increase of temperature.
Now the present inventors have developed a new medical device which allows a continuous use of light sources and allows delivering a uniform light distribution to complex body shapes and high fluence rate of illumination.
Additionally, since the efficacy of photodynamic therapy (PDT) depends on the amount of singlet oxygen which itself depends on the amount of pre-administered photosensitizer because for a photodynamic reaction to occur, the photosensitising agent, activating light and oxygen must be present in sufficient amounts, it is important to determine the amount of active photosensitising agent remaining at the site of action. In fact degradation of the photosensitiser occurs during treatment and this effect is named photobleaching.
The measurement of photobleaching allows knowing the efficacy of photodynamic therapy and adjusting the light treatment. The principle of measurement is to estimate the amount of singlet oxygen produced by photodynamic therapy by measuring the rate of photobleaching of the photosensitizer by measuring the fluorescence. For example for protoporphyrin IX, an excitation light at 405 nm and collecting the fluorescence at 630 nm can be used.
Additionally the present inventors have therefore developed a new medical device allowing treatment by photodynamic therapy and further allowing the measurement of photobleaching of a photosensitizer used in the course of photodynamic therapy.
A subject of the present application is therefore a medical device comprising a flexible light source wherein said flexible light source comprises two or more individually manageable areas of light emission and wherein each area comprises a light diffuser textile comprising optical fibres providing side diffusion of a light.
Whereas usually in optical fibres light is guided down the core of the fibre by a coating named optical cladding having a refractive index lower than the refractive index of the core, that traps light in the core through total internal reflection, in the present invention the optical fibres are bent such that a critical angle is exceeded whereby light escapes from the core of the fibres providing side diffusion of the light.
More particularly, integration of flexible optical fibres into textile tissue structures provides a light diffuser textile used in the invention.
In one embodiment of light diffuser textile, a plain weave of optical fibres and other possibly coated textile fibres is used. The light travelling through the optical fibres is emitted through scratches, pierced by mechanical indentation (toothed roll). Scratches may also be obtained by projecting particles at the cladding or by chemical treatment (solvent action to locally dissolve the cladding). These kinds of indentations are possible with the polymer optical fibres such as polymethyl methacrylate optical fibres.
In another embodiment of light diffuser textile, the polymer optical fibres emit light without indentation of the surface fibre or cladding. For instance, a light emitting panel made from one or more layers of polymer optical fibres woven into a sheet (plain weave) and coated with diffusive material in order to better diffuse laterally emitted light may be used. The plain weave structure of the fabric, in this case, enables the bends of the woven optical fibres allowing light emission laterally. The diffusive layer improves the homogeneity of light distribution. Such an illuminating panel is for example available from Lumitex Company.
In another embodiment of light diffuser textile, an embroidery-based light diffuser textile consists of a dense woven substrate in which polymer optical fibres are fixed using conventional yarn. The polymer optical fibres forms random bends and loops leading to macrobending of the fibre from which light can escape. Such a textile construction maybe composed of 178 polymer optical fibres (polymethyl methacrylate, diameter of 175 μm) providing a flexible diffuser about 2 mm in height and delivering a round luminous area of about 11 cm2.
A preferred light diffuser textile of the invention is obtained by weaving. The warp provides the skeleton of the textile whereas the weft comprises the optical fibres. The warp preferably comprises polyester yarns whereas the weft preferably comprises polymethyl methacrylate optical fibres.
Examples of suitable polyester yarns are copolyester yarns are commercialised by Sinterama, for example, commercial reference LAST®.
The linear mass density of polyester yarns may be in a range of 50 to 500 dTex, preferably of 100 to 400 dTex, particularly of 300 to 370 dTex, and more particularly of approximately 330 dTex.
When polyester yarns are made of continuous microfibres, light delivering is increased.
Polyester yarns must be strong enough for allowing sufficient bending of the optical fibres to exceed a critical angle whereby light escapes from the core of the fibres providing side diffusion of the light.
Examples of suitable polymethyl methacrylate optical fibres are commercialised by Toray (Japan), for example with commercial references RAYTELA®, PG series. The polymethyl methacrylate core thereof is surrounded by a fluorinated polymer cladding.
The diameter (including the cladding) of optical fibres, preferably polymethyl methacrylate optical fibres, may be in a range of 750 to 100 μM, preferably of 500 to 200 μM, particularly of 300 to 200 μM, more particularly of 270 to 230 μM, and very particularly of approximately 250 μM. The smaller the diameter of the optical fibres, the more a light diffuser textile thus manufactured is flexible.
The smaller the thickness of the cladding, the more a light diffuser textile thus manufactured is efficient. An optical fibre with a very thin cladding, for example about 1/50 of the overall diameter, is preferred for improving the efficiency of the light collection.
Warp yarns of a preferred light diffuser textile of the invention have a density of about 20 cm−1. Said density may be determined for example by optical count.
Weft density varies according to weave and may be determined for example by optical count.
Dimensions of a light diffuser textile of the invention, i.e. dimensions of the woven area, may vary in a broad range, only limited by the weaving material used. Typical dimensions of a light diffuser textile of the invention, are 21.5 cm (weft, named width, W)×5 cm (warp, named length, L). Other preferred dimensions are for example 25 cm×15 cm, 30 cm×20 cm or 15 cm×10 cm. Since a medical device of the invention comprises two or more light diffuser textiles, the surface of the medical device will be for example twice or three times the surface of an individual light diffuser textile.
In order to connect the fabric to the light source, the total length of optical fibres is longer than the length actually woven in the woven area. For example 15 cm to 1 m is free (non-woven) on one side or both sides of the woven area, preferably of sites.
Particularly preferred textiles of the invention are obtained by mechanized weaving and are advantageously plain weave or satin weave.
Examples of satin weave are satin weave 4 (SW4), satin weave 6 (SW6) and satin weave 8 (SW8). Combinations of patterns using different weaves are preferred because they allow providing a flexible fabric having a very uniform distribution of light.
A flexible light source of a medical device of the invention comprises two or more individually manageable areas of light emission, each area comprising a light diffuser textile. Therefore each individually manageable area may be used for light emission independently of each other area.
Assuming a medical device of the invention comprises two individually manageable areas of light emission, one area may be active whereas the other area is at rest.
A preferred medical fabric of the invention comprises 2 to 24, particularly 3 to 9, more particularly 3 to 6, and very particularly 3 individually manageable areas.
Preferably, the different areas of a given medical device have an identical or similar surface. For example in a case of a flexible light source having three individually manageable areas, each area of light emission represents about one third of the entire surface of the flexible light source.
Under preferred conditions for implementing the invention, a single light-emitting device, preferably comprising a laser, particularly a diode laser, may be connected to each and every area of light emission. Therefore, since the different areas of light emission are individually manageable, one area may be active whereas the other areas are at rest. Furthermore the same light-emitting device may later be used for illuminating another area. Accordingly although the light emitting device may be continuously working, only a part of the medical fabric of the invention may be active whereas another or other parts are at rest (inactive).
In view of easily connecting a light-emitting device, the optical fibres constituting the weft of each light diffuser textile are preferably collected as bundles and said bundles are further provided with a port of entry (input) of light such as optical fibre connectors.
Preferably the flexible light source consists of two or more individually manageable light diffuser textiles.
A subject of the present invention is also a medical apparatus for photodynamic therapy comprising an above medical fabric and a light-emitting device suitable for photodynamic therapy, preferably comprising diodes, whereby the flexible light source of the invention may provide side diffusion of light.
A subject of the present invention is also a process for the manufacture of an above medical device of the invention comprising the steps consisting in manufacturing two or more light diffuser textiles obtained by
For example a medical device comprising two or more light diffuser textiles may be prepared by bundling the optical fibres into two or more groups of adjacent fibres.
Two or more independent light diffuser textiles may also be manufactured and assembled as a single flexible light source for a medical device.
In preferential conditions of implementation of the invention, optical fibres constituting the weft of each light diffuser textile are further provided with one or several ports of entry of light for easy connection to a light emitting device.
A subject of the present invention is also a bifunctional medical device comprising a flexible light source wherein said flexible light source comprises
An emission of light is for example produced by a photosensitiser substance that has absorbed light or other electromagnetic radiation. This emission of light may be absorbed by the optical fibres providing side absorption of a light of the invention. For example protoporphyrin IX may receive an excitation light at 405 nm and in turn provide emission of fluorescence at 630 nm which may be absorbed by the optical fibres.
The general structure of the above bifunctional medical device is similar to the structure of the above medical device comprising a flexible light source wherein said flexible light source comprises two or more individually manageable areas of light emission and wherein each area comprises a light diffuser textile comprising optical fibres providing side diffusion of a light, with a few particularities.
A given area may be provided with a single bundle having a connector. The connector may be alternatively connected either to a light-emitting device suitable for photodynamic therapy or to a photodetector. A given area may also be provided with a pair of bundles or more, each bundle corresponding to different optical fibres being specialised either for therapy or for detection of bleaching. Additionally a third bundle may be used for providing a light with a wavelength different of the therapeutic wavelength for a better detection of bleaching.
In an individually manageable area of light emission, the ratio fibres used for detection/fibres used for therapy, may be in the range 1/1 to 1/20, preferably in the range 1/2 to 1/15, more preferably in the range 1/3 to 1/15. In such a case, fibres used for detection are preferably well spread over the entire surface of the area, more preferably distributed in a balanced way, for example one fibre for detection every five fibres used for therapy.
Suitable photodetectors are for example commercialised by Siemens.
Preferred conditions for implementing the medical devices without optical fibres dedicated to the detection described above also apply to the above medical devices comprising such fibres.
The medical devices according to the invention have advantageous properties. They constitute flexible and homogenous light diffusers providing side-emission of light. Because of their flexibility, they are easily adapted to human curves. They offer a cheap alternative as light source for photodynamic therapy. In addition to a uniform light illumination of the skin, they provide strong and homogenous irradiance, around 20 mW/cm2 while avoiding excessive increase of temperature.
The achieved homogeneity is much better than results obtained with commercially available LED panels. With a flat panel of LEDs such as described in U.S. Pat. No. 4,907,132, some surfaces of skin are close to the light emitters whereas other are remote. Unlike LED panels, a light diffuser of the invention is flexible and can closely follow the surface to be treated. In contrast with US 2006/0257095, a light diffuser of the invention provides a much more important irradiance while avoiding excessive increase of temperature.
Another advantage is that light diffusers of the invention act as a waveguide, and thus the light source is separated from the light emitting device. Hence, with a same light emitting device it is possible to diffuse light of different wavelengths by simply changing the source.
The medical devices according to the invention further provided with one or more bundles specialised for photo detection are bifunctional since they allow treatment in combination with a photosensitizer and additionally they allow assessing the level of bleaching of the photosensitizer.
Consequently the possible applications of a light diffuser of the invention are numerous including medical applications such as lightning of a human body cavity such as peritoneal or pleural cavities, or lightning of a human body cavity after surgical resection (glioblastome for example). Non medical applications are for example light applications in lighting, communications, safety, or pollution control by combining a light diffuser of the invention with ultraviolet radiation. A light diffuser of the invention may also be used more particularly in the treatment of malignant mesothelioma and peritoneal carcinoma such as papillary serous carcinoma.
Because of the above properties the medical devices comprising a flexible light source according to the invention may be particularly used as light diffusers for photodynamic therapy.
Some embodiments also may be used as light diffusers for photodynamic therapy and detectors of bleaching of a photosensitiser.
Therefore a further subject of the invention is a medical apparatus for photodynamic therapy comprising a medical device as disclosed above and a light-emitting device suitable for photodynamic therapy such as those previously mentioned. A further subject of the invention is such a medical apparatus for photodynamic therapy further comprising a photodetector.
Light-emitting devices suitable for photodynamic therapy are for example lasers and preferably diode lasers providing light having a wavelength of 400 to 800 nanometres for example depending on the active ingredient used. Such light emitting devices are for example commercialised by OMNILUX (http://www.omnilux.co.uk/).
Suitable photosensitizers for photodynamic therapy are for example hematoporphyrine (630 nm), meta-tetra hydroxyphenyl chlorine, (652 nm), benzoporphyrine (690 nm), bacteriopheophorbides (753 nm), methyl aminolevulinate (405 to 670 nm). Excitation wavelengths are given between brackets.
A further subject of the invention is a medical apparatus as defined above further comprising means for managing light emission by a medical device of the invention, independently for each of the two or more areas. Means for managing light emission usually comprise a calculator and preferably a computer. Data specific for a treatment of a patient may therefore be provided to a computer which controls intensity, duration and frequency of irradiation. An example of treatment of actinic keratosis using a medical device comprising a flexible light source having 3 individually manageable areas in association with a photosensitizer is 30 cycles each cycle being a sequence consisting of 1 min illumination of area 1, then 1 min illumination of area 2, then 1 min illumination of area 3, then again 1 min illumination of area 1 etc. with an intensity of light (irradiance) of 10 mW/cm2.
More generally, each sequence of illumination may last from 15 sec to 180 min, preferably from 20 sec to 180 min, particularly from 30 sec to 180 min, more particularly from 30 sec to 180 min.
A further subject of the invention is a method for the assessment of the photobleaching of a photosensitizer used in a photodynamic therapy method comprising the steps consisting in
In such a method, a port is used as an output for providing light to the photodetector.
The medical device preferably comprises a flexible light source comprising two or more individually manageable areas (2, 3, 4) of light emission. In view of the above properties, a further subject of the invention is a method for activating a photosensitising agent provided on a surface wherein a medical apparatus for photodynamic therapy as described above is used for activating the photosensitising agent and wherein each of 3 to 9 individually manageable areas is sequentially put on, whereby each of 3 to 9 individually manageable areas provides sequential illumination to the photosensitising agent.
Each of the 3 to 9 individually manageable areas is sequentially put on for a duration of 15 seconds to 180 minutes.
Another further subject of the invention is a method for the assessment of the photobleaching of a photosensitising agent which may be used in a photodynamic therapy method, comprising the steps consisting in
In a preferred method, one or more bundles connected to a device providing light or other electromagnetic radiation are used for photo detection and one or more bundles connected to a photodetector are used for detecting photobleaching of a photosensitising agent.
In the above method, the ratio fibres used for detection/fibres used for therapy, is advantageously in the range 1/2 to 1/15.
Preferred conditions for implementing the medical devices described above also apply to the other subjects of the invention envisaged above, for example their uses and methods of use.
The invention will now be described by means of the following Examples
In order to connect each light diffuser textile 2, 3, 4 to a light source, a part of the length of the optical fibres is free. The free sections 5 of the optical fibres are provided on the same side of the flexible light source. The free sections 5 of the optical fibres are bundled and inserted into a brass ferrule 6 allowing optical connection to a light source 7. After gluing and cutting, the end of the optical fibres is highly polished such that an excellent surface is obtained. The three brass boxes 6 are used as ports of entry of light for optical fibre connectors provided on the light source 7. The light source 7 is managed by a computer 8 and provides light sequentially to each light diffuser textile 2, 3, 4 according to a sequence 2-3-4-2-3-4-2-3-4-2 etc. On
The medical device of
Free sections 5 of the optical fibres of the embodiment of
Accordingly, light may be provided at both ends of optical fibres. Long free sections 5 allow using a single light source 7. Schematic
a and b illustrate the homogeneity of light emission with a flexible light source of the invention while
From the left of the drawing, about 20 cm long free non-woven optical fibres are found, followed by a 21.5 cm long woven area comprising W1 weave (4.5 cm), W2 weave (3.0 cm), W3 weave (6.5 cm), W2 weave (3.0 cm), and W1 weave (4.5 cm). Wi patterns are explained hereafter. On the opposite side, the free other ends of the optical fibres are found. Their length is also about 20 cm. the woven area is 5 cm wide and comprises 187 weft optical fibres (density 37 fibres per cm).
The free optical fibres are to be bundled and inserted into a connector for connection to a light source.
All flexible light diffuser textiles were woven using the hand weaving loom ARM B60 from Biglen (Switzerland).
The warp yarns are composed of 330 dTex polyester from Sinterama with a density of 20 cm−1.
Toray Raytela® PG series Polymethyl methacrylate optical fibres with fluorinated polymer cladding (refractive index 1.41) are introduced as weft using a modified shuttle. The cladding diameter thereof is 250 μm.
Weft density varies according to weave and is determined by optical count. The dimension of the flexible light diffuser textile manufactured is 21.5 cm (weft, named width, W)×15 cm (warp, named length, L). In order to connect the fabric to a light source, the total length of polymethyl methacrylate optical fibres is about 60 cm: 21.5 cm are weave and approximately 20 cm+20 cm on each side of the woven area are free. The density of the optical fibres is 37 per cm.
Five samples have been woven: four samples made from basic weave and one sample of textile light diffuser with a weave pattern specifically developed for photodynamic therapy application.
The four samples are plain weave (PW), satin weave 4 (SW4), satin weave 6 (SW6) and satin weave 8 (SW8). The structure of the specific light diffuser textile is the following: The width of the light diffuser textile is composed of the following 5 areas with appropriate dimensions and structures of weaving: free optical fibres/4.5 cm W1/3.0 cm W2/6.5 cm W3/3.0 cm W2/4.5 cm W1/free optical fibres. The five areas compensate attenuation of side emitted light and allow obtaining homogeneous light diffusers.
The weft density is 37 fibres /cm and the warp density 20 yarns/cm. The fabric comprises
This sequence of strips W1-W2-W3-W2-W1 provides a flexible fabric having a very uniform distribution of light. More details of such a structure are given in WO 2012/098488.
The weft density of polymethyl methacrylate optical fibres is set to 37 cm−1.
Step A:
The 15 cm wide light diffuser textile of example 1 comprises 555 optical fibres. A medical device having the structure shown on
Step B:
Each pair of bundles of each light diffuser textile was inserted into a ferrule of highly polished brass whose internal diameter is adapted to the number of individual fibres inserted therein (internal diameter 5 mm for 370 fibres—185 from each side—of 250 μm diameter). Three ferrules were used for the six bundles. This arrangement allows provision of light from both sides of a light diffuser textile with a same source of light.
Araldite 2011 epoxy adhesive from Huntsman Advanced Materials is used to bond the optic fibres into the ferrule. 12 hours later, after hardening of the glue, the excess length of the optical fibres was cut and polished at the extremity of the ferrule. Polishing requires 99% isopropyl alcohol, polishing (lapping) film and pad, a polishing puck. Special polishing paper is employed successively from coarser grits to finer grits measured in microns. The last is a 0.5 μm polishing paper.
After fine polishing of the extremity of the ferrule, a medical device provided with three connectors was thus obtained.
A medical device having the structure shown on
This arrangement allows provision of light from both sides of a light diffuser textile using two sources of light.
A medical device having the structure shown on
One ferrule of internal diameter 3.56 mm was used for the 185 fibres of each bundle. Three ferrules were thus used for the three bundles. This arrangement allows provision of light from only one side of a light diffuser textile.
In the above examples 2, 3 and 4, after hardening of the glue, the excess length of the optical fibres was cut and polished using a fine grit (5 μm) abrasive paper. Special polishing paper is employed successively from coarser grits to finer grits measured in microns. The last is a 0.5 μm polishing paper.
The ferrules of each of the medical devices of examples 2, 3 and 4 were connected to a 635 nm laser diode (5 W, Dilas, Germany).
The medical device of example 2 is described in details. The light diffuser textile used is the specific textile of example 1.
Each light diffuser textile is equipped with a single connector (or ferrule) of 5.02 mm internal diameter which includes 370 fibres of diameter 250 μm. One laser diode commercialised by DILAS (reference M1F4S22-638.3-5C-SS2.6) is used to illuminate each light diffuser textile. This laser diode emits 5 W. it is equipped with a standard SMA connector. (ref DS11-lp-o8617-v0). The diode is mounted on a Peltier module (PE1-12707AC society Multicomp) to ensure the cooling of the diode.
The diode and the Peltier module are supplied via a power supply OSTECH (ref DS11-lp-o8617). This power supply manages all functions of the diode and Peltier module, using a computer with a RS-232 connection. The control software is provided by OSTECH. It is therefore possible to manage the diode and Peltier module through a list of commands provided by OSTECH with a laptop at the convenience of the user. See http://www.ostech.com/home_en.htm and http://www.ostech.com/downloads_software_en.htm
A 3 m long optical fibre of 600 μm equipped with a SMA connector at each end (supplied by Sedi http://www.sedi-fibres.com/medical—225.html fibre) is connected to an optical device for expanding the 600 μm beam to 5 mm.
The three light diffuser textiles are provided with identical laser diodes. A software written in Labview allows managing and controlling the three laser diodes via the RS-232.
The software allows to independently set each diode power (0 to 5 W), the time of illumination (1 sec to 99 minutes), the delay of illumination (1 s to 99 minutes) and the number illuminations (1-99). After programming each laser diode, it is possible to synchronize the operation of the diodes.
As indicated above in example 3, three individually manageable areas of light emission were produced with a difference that for each area the optical fibres were bundled as follows: a first bundle comprising every fifth optical fibre was prepared. A second bundle was prepared comprising the remaining optical fibres. Accordingly a first bundle comprises ⅕ of the optical fibres whereas the second bundle comprises ⅘ of the optical fibres. The first bundle may be used for assessment of the bleaching of a photosensitiser whereas the second bundle may be used for phototherapeutic treatments.
This medical device comprises six bundles, each provided with a ferrule: three for assessment of the bleaching of a photosensitiser and three for phototherapeutic (or photodynamic) treatments.
Experimental Data
The experiments were implemented with light diffuser textiles having the specific structure described in Example 1.
Experimentation 1: Sequence of Illumination
In reference to example 5: The first laser diode is switched on. When the first laser diode has completed a 1 minute illumination, it is switched off. An instruction of switching on is sent to the second laser diode. After completion of a 1 minute illumination by the second laser diode, said laser diode is switched off and a instruction of switching on is sent to the third laser diode, which after completion of a 1 minute illumination is switched off. The first laser diode is switched on for a second time and so on depending on the number of illuminations programmed by the user.
Therefore in the present case, laser diodes are scheduled to have a rest period of 2 minutes.
With a power of 10 mW/cm2, a treatment is implemented for the duration of one hour and a half such that 18 J/cm2 of treated surface. Accordingly, one given light diffuser textile is illuminated for 30 min.
Experimentation 2: Homogeneity of Light Delivery by the Medical Apparatus of Example 2 (Size 5 cm×21.5 cm)
The measurement of the irradiance was achieved with a wattmeter OPHIR PD 300. The measuring head has a surface of 1 cm2. It is therefore possible to obtain a measure of the irradiance expressed in mW/cm2. The measurement was carried out on 105 areas of 1 cm2 of one light diffuser textile. The distribution of the light emitted by the illuminated tissue was thus obtained. For an injected power of 5 W, the tested textile of the invention provides an intensity of 18.2 mW·cm2±2.5 mW·cm−2. Therefore, a medical device of the invention provides a strong light.
The light delivered by the medical apparatus of example 5 was found to be remarkably homogeneous.
Experimentation 3. Measurement of the Temperature Reached by a Medical Light Diffuser Textile of the Invention in the Course of a Treatment (Size: 5 cm×21.5 cm)
Temperature evolution of a medical light diffuser textile as a function of duration of illumination was controlled using an infrared thermographic camera (Fluke Ti 125). After 10 min of illumination with an irradiance of 18.2 mW/cm2, the increase of temperature was only 0.6° C.
The homogeneity of illumination achieved on an irregular surface with hollows and bumps is much better than results obtained with commercially available inflexible LED panels.
Experimentation 4: Measurement of Bleaching of a Photosensitiser
As indicated above in example 3, three individually manageable areas of light emission were produced with a difference that for each area the optical fibres were bundled as follows: a first bundle comprising every fifth optical fibre was prepared. This first bundle has a diameter of 2.25 mm and comprises 74 fibres. A second bundle was prepared comprising the remaining optical fibres. Accordingly a first bundle comprises ⅕ of the optical fibres whereas the second bundle comprises ⅘ of the optical fibres. The first bundle may be used for assessment of the bleaching of a photosensitiser whereas the second bundle may be used for phototherapeutic treatments.
The first bundle is connected to a spectrometer 350-1100 nm USB2000+VIS-NIR (Ocean Optics Inc., Dunedin, Fla., USA) having a high sensitivity at 705 nm using an optical system consisting of Thorlabs Inc. parts.
The spectrophotometer is connected to a laptop by an USB cable.
The illumination bundle comprising 296 fibres has a diameter of 4.51 mm and is connected to a laser diode as previously described.
The photosensitiser used is protoporphyrin IX. The photosensitiser was excited at 630 nm. Fluorescence emitted by the photosensitiser was measured at 705 nm.
A computer with a Labview software allows to manage a just-in-time the operation of illumination and acquisition of fluorescence spectra. The power of the laser diode emitting at 630 nm is adjusted for obtaining an irradiance of 1 mW/cm2 in the red which corresponds to a power of 0.3 W. The Ocean Optics spectrophotometer is programmed for acquiring hundred fluorescence spectra (Integration time set to 0.5 seconds), i.e. 50 seconds. See http://www.oceanoptics.com/products/usb2000+precon.asp.
At the end of the acquisition of the data, the software calculates the intensity of fluorescence at 705 nm. The initial value is the reference 100%. During photobleaching of the photosensitiser, the initial value decreases
If the fluorescence measurement is greater than 10% of the initial fluorescence, the treatment is continued. The spectrophotometer is stopped. The management software of the red laser diode switches on to treatment and increases the power to 3 W to achieve an irradiance of 10 mW/cm2, considered therapeutic.
After the scheduled duration of treatment (one minute), the fluorescence measurement is performed again as described above.
When the fluorescence is 10% of the initial value, the treatment procedure is interrupted.
Experimentation 5: Amount of Light Collected by a Medical Light Diffuser Textile of the Invention (Size 5 cm×21.5 cm)
Two identical medical devices described in examples 2 and 3 (21.5×5 cm) were used for the experiment.
The first one was used as light emitter. Its optical connector was connected to a Modulight laser 1.3 W emitting at 635 nm equipped with a THORLABS coupling Tube.
The second one was superimposed onto the first one and was used as light collector for the measurement of the input light. The amount of input light is the same on both sides of the light emitter. Its optical connector was connected to a Newport wattmeter 841-PE with a PD 300 measure head (PhotoDetector) via a THORLABS coupling Tube.
An OPHIR wattmeter with PD 300 measure head was used for the measurement of the input light.
Sedi SMA-SMA cords were used for the connexions.
A power of 240 mw was measured by the OPHIR wattmeter. A power of 192 μw was measured by the more sensitive Newport wattmeter ((Photo Detector)
A medical light diffuser textile of the invention is able to collect and also to detect light.
| Number | Date | Country | Kind |
|---|---|---|---|
| EP13305373.6 | Mar 2013 | EP | regional |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2014/055770 | 3/21/2014 | WO | 00 |
