CA2187417A1 - Method and apparatus for treatment of cancer using electromagnetic radiation - Google Patents
Method and apparatus for treatment of cancer using electromagnetic radiationInfo
- Publication number
- CA2187417A1 CA2187417A1 CA002187417A CA2187417A CA2187417A1 CA 2187417 A1 CA2187417 A1 CA 2187417A1 CA 002187417 A CA002187417 A CA 002187417A CA 2187417 A CA2187417 A CA 2187417A CA 2187417 A1 CA2187417 A1 CA 2187417A1
- Authority
- CA
- Canada
- Prior art keywords
- pulsed radiation
- radiation output
- radiation
- pulsed
- treatment
- Prior art date
- Legal status (The legal status 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 status listed.)
- Abandoned
Links
- 206010028980 Neoplasm Diseases 0.000 title claims abstract description 63
- 238000011282 treatment Methods 0.000 title claims abstract description 54
- 238000000034 method Methods 0.000 title claims abstract description 26
- 230000005670 electromagnetic radiation Effects 0.000 title claims description 7
- 201000011510 cancer Diseases 0.000 title description 3
- 230000005855 radiation Effects 0.000 claims abstract description 124
- 230000002977 hyperthermial effect Effects 0.000 claims abstract description 9
- 238000001914 filtration Methods 0.000 claims abstract description 8
- 230000002500 effect on skin Effects 0.000 claims abstract 2
- 238000001228 spectrum Methods 0.000 claims description 10
- 230000001934 delay Effects 0.000 claims 1
- 210000003491 skin Anatomy 0.000 description 21
- 230000035515 penetration Effects 0.000 description 16
- 206010020843 Hyperthermia Diseases 0.000 description 7
- 238000010438 heat treatment Methods 0.000 description 7
- 230000036031 hyperthermia Effects 0.000 description 7
- 210000004207 dermis Anatomy 0.000 description 5
- 230000003287 optical effect Effects 0.000 description 4
- 206010028851 Necrosis Diseases 0.000 description 3
- 230000017074 necrotic cell death Effects 0.000 description 3
- 230000001225 therapeutic effect Effects 0.000 description 3
- 206010054094 Tumour necrosis Diseases 0.000 description 2
- 230000000903 blocking effect Effects 0.000 description 2
- 239000000835 fiber Substances 0.000 description 2
- 230000012010 growth Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 230000007935 neutral effect Effects 0.000 description 2
- 238000002428 photodynamic therapy Methods 0.000 description 2
- 238000002560 therapeutic procedure Methods 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 230000006378 damage Effects 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 238000000295 emission spectrum Methods 0.000 description 1
- 230000005764 inhibitory process Effects 0.000 description 1
- 230000001678 irradiating effect Effects 0.000 description 1
- 230000031700 light absorption Effects 0.000 description 1
- 201000001441 melanoma Diseases 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 150000002739 metals Chemical class 0.000 description 1
- 239000013307 optical fiber Substances 0.000 description 1
- 230000037368 penetrate the skin Effects 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 239000010453 quartz Substances 0.000 description 1
- 238000001959 radiotherapy Methods 0.000 description 1
- 238000002310 reflectometry Methods 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N silicon dioxide Inorganic materials O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 description 1
- 230000037380 skin damage Effects 0.000 description 1
- 230000003595 spectral effect Effects 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 230000000451 tissue damage Effects 0.000 description 1
- 231100000827 tissue damage Toxicity 0.000 description 1
- 231100000167 toxic agent Toxicity 0.000 description 1
- 239000003440 toxic substance Substances 0.000 description 1
- 210000004881 tumor cell Anatomy 0.000 description 1
- 230000004614 tumor growth Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/40—Applying electric fields by inductive or capacitive coupling ; Applying radio-frequency signals
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N5/0613—Apparatus adapted for a specific treatment
- A61N5/0616—Skin treatment other than tanning
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N2005/0635—Radiation therapy using light characterised by the body area to be irradiated
- A61N2005/0643—Applicators, probes irradiating specific body areas in close proximity
- A61N2005/0644—Handheld applicators
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/06—Radiation therapy using light
- A61N2005/0658—Radiation therapy using light characterised by the wavelength of light used
- A61N2005/0659—Radiation therapy using light characterised by the wavelength of light used infrared
Abstract
The invention includes a method for the hyperthermic treatment of tumors including the steps of providing a pulsed radiation output from a radiation source;
and directing said pulsed radiation output toward a tumor.
The invention further includes an apparatus for the treatment of tumors having a radiation source adapted to produce broad-band pulsed radiation output at least in the visible and near-infrared range of wavelengths, a delivery system proximal to the radiation source and adapted to focus and direct the pulsed radiation output to a dermal treatment site, and a filtering system adapted to restrict the pulsed radiation output to bands in the visible and near-infrared range of wavelengths.
and directing said pulsed radiation output toward a tumor.
The invention further includes an apparatus for the treatment of tumors having a radiation source adapted to produce broad-band pulsed radiation output at least in the visible and near-infrared range of wavelengths, a delivery system proximal to the radiation source and adapted to focus and direct the pulsed radiation output to a dermal treatment site, and a filtering system adapted to restrict the pulsed radiation output to bands in the visible and near-infrared range of wavelengths.
Description
`_ ~ET~IOD AND APPARa~lJ8 FOR
TP~TM~NT OF C~NCER ~J8ING ~ 7 4 1 7 Pm.8ED E$,~5CTRC'~TIC R~DIATION
This invention relates to an apparatus and method for the treatment of tumors. More particularly, the invention relates to an apparatus for the irradiation of shallow tumors with pulsed electromagnetic radiation.
FIELD OF THE INVENTION
Several non-surgical methods are available for -treatment of cancer, but all of them have disadvantages.Chemical therapy and photodynamic therapy are accompanied ~y the introduction of a toxic agent into the body.
Electromagnetic radiation therapy using X-rays causes the _ destruction of healthy tissue due to X-rays ability to penetrate deeply into human tissue.
Another method, called hyperthermia, is used for tumor necrosis both by itself, and in combination with other methods of cancer treatment. The basic purpose of hyperthermia is to raise tumor temperature substantially above body normal temperature, to a temperature at which tumor cells are killed. The "selectivity" of hyperthermic therapeutic methods are the extent to which the tumors and not the surrounding healthy tissue is destroyed.
Hyperthermic treatments have been employed for both whole body heating and for local heating of tumors. Local hyperthermia typically uses sources of electromagnetic radiation, focused on the tumor at frequencies that will heat tumor tissue and not the surrounding healthy tissue.
Microwave, visible and infrared frequency ranges are commonly employed for this purpose.
TP~TM~NT OF C~NCER ~J8ING ~ 7 4 1 7 Pm.8ED E$,~5CTRC'~TIC R~DIATION
This invention relates to an apparatus and method for the treatment of tumors. More particularly, the invention relates to an apparatus for the irradiation of shallow tumors with pulsed electromagnetic radiation.
FIELD OF THE INVENTION
Several non-surgical methods are available for -treatment of cancer, but all of them have disadvantages.Chemical therapy and photodynamic therapy are accompanied ~y the introduction of a toxic agent into the body.
Electromagnetic radiation therapy using X-rays causes the _ destruction of healthy tissue due to X-rays ability to penetrate deeply into human tissue.
Another method, called hyperthermia, is used for tumor necrosis both by itself, and in combination with other methods of cancer treatment. The basic purpose of hyperthermia is to raise tumor temperature substantially above body normal temperature, to a temperature at which tumor cells are killed. The "selectivity" of hyperthermic therapeutic methods are the extent to which the tumors and not the surrounding healthy tissue is destroyed.
Hyperthermic treatments have been employed for both whole body heating and for local heating of tumors. Local hyperthermia typically uses sources of electromagnetic radiation, focused on the tumor at frequencies that will heat tumor tissue and not the surrounding healthy tissue.
Microwave, visible and infrared frequency ranges are commonly employed for this purpose.
-2- 2 1 ~74 1 7 Current hyperthermic methods have significant disadvantages. Treatment times are often long, on the order of an hour. Furthermore, the selectivity of the radiation is low, causing necrosis not only of tumor tissue, but of the healthy surrounding tissue as well.
Hyperthermia treatments using microwave radiation sources (typically radiating at about 915 MHz) have the disadvantage of deep non-tunable penetration (several centimeters) into the body as well as problems with focusing which cause low selectivity.
Nd:YAG laser radiation sources are used both by themselves and in combination with photodynamic therapy.
One disadvantage of Nd:YAG laser when used for hyperthermia is its small spot size, on the order of 5 mm. A radiation source this small cannot easily heat large tumors, which may have a projected area of several square centimeters on the skin, resulting in extended treatment times. In addition, the Nd:YAG laser has other limitations relating to their continuous wave (CW) operating mode, and with their limited tunable range. It is clear that an improved apparatus and method for hyperthermia tumor treatment is desirable.
Pulsed radiation of a tumor using a light source would cause more efficient hyperthermia and necrosis than current methods provide. Furthermore, a radiation source capable of heating tissue in a short time interval, preferably between 41 and 45 degrees C, would reduce the treatment times currently required. Providing a radiation source with a broad controllable spectrum of radiation in the visible and near infrared regions would allow the penetration depth and the selectivity of the treatment to be more accurately controlled.
Hyperthermia treatments using microwave radiation sources (typically radiating at about 915 MHz) have the disadvantage of deep non-tunable penetration (several centimeters) into the body as well as problems with focusing which cause low selectivity.
Nd:YAG laser radiation sources are used both by themselves and in combination with photodynamic therapy.
One disadvantage of Nd:YAG laser when used for hyperthermia is its small spot size, on the order of 5 mm. A radiation source this small cannot easily heat large tumors, which may have a projected area of several square centimeters on the skin, resulting in extended treatment times. In addition, the Nd:YAG laser has other limitations relating to their continuous wave (CW) operating mode, and with their limited tunable range. It is clear that an improved apparatus and method for hyperthermia tumor treatment is desirable.
Pulsed radiation of a tumor using a light source would cause more efficient hyperthermia and necrosis than current methods provide. Furthermore, a radiation source capable of heating tissue in a short time interval, preferably between 41 and 45 degrees C, would reduce the treatment times currently required. Providing a radiation source with a broad controllable spectrum of radiation in the visible and near infrared regions would allow the penetration depth and the selectivity of the treatment to be more accurately controlled.
-3- ~Y1417 --SUMMARY OF THE PRESENT I~v~:NllON
- The present invention is directed to a method for the hyperthermic treatment of tumors with electromagnetic radiation including the steps of providing a pulsed radiation output from a radiation source and directing said pulsed radiation output toward a tumor. The radiation may be developed over at least one continuous band of wavelengths, or be generated in the visible and near-infrared band, possibly in a continuous band between 600 an~
1000 nm. In one embodiment, it may include the step of transmitting a broad radiation beam to a pigmented tumor, which might have a cross-sectional area of between 0.8 cm2 and 500 cm2. In another embodiment, it is possible to control the pulse-width of the pulsed radiation output, focus the radiation source for controlling the power density of the pulsed radiation output, or filter and control the spectrum of the pulsed radiation output. In particular, one may focus the pulsed radiation output to a beam having a cross-sectional area of greater than 0.8 cm2.
Alternatively, one may cut off the UV portion of the spectrum. A pulse width in the range of about 100 microseconds to 50 milliseconds may be provided, particularly, one having an energy density at the treatment area of at least 0.2 W/cm2. Alternatively, energy densities of greater than 90 J/c*, 120 J/cm2 per treatment may be provided at the treatment site. A pulse delay of greater than 100 milliseconds or less than 100 seconds may also be provided.
In another embodiment of the invention, an apparatus for the treatment of tumors is provided, including a radiation source producing pulsed radiation at least in the visible and near-infrared wavelengths, a delivery system _4_ 21 8741 7 near the radiation source for focusing and directing the radiation to a treatment site, and a filtering system restricting the radiation to visible and near-infrared wavelengths. Alternatively, the radiation source may produce pulsed radiation in a broad band, or over at least - one continuous range of wavelengths. This may be focused in a beam of at least 0.8 cm2. The radiation may be restricted to a band between 300 and 1000 nm, or may be W blocked by a filter. The radiation pulses may have a duration of between 100 ~secs and 100 msecs, and may be spaced from 100 msecs to 100 secs apart. In addition, they may be delivered to the treatment area with a radiation-density of greater than 0.2 W/cm2, 90 Jtcm2, or 120 Jlcm2. The radiation may also be limited to a radiation density of less than 200 J/cm2.
Other principal features and advantages of the invention will become apparent to those skilled in the art upon review of the following drawings, the detailed description and the appended claims.
BRIEF DESCRIPTION OF THE DRAWINGS
~ IG~RE 1 is a graph of radiation tissue penetration versus radiation wavelength;
FIG~RE 2 is a cross-sectional view of tumor treatment -device according to the present invention; and - FIG~RE 3 is a graph of treatment results using the FIGURE 2 tumor treatment device.
- Before explaining at least one embodiment of the invention in detail it is to be understood that the invention is not limited in its application to the details of construction and the arrangement of the components set forth in the following description or illustrated in the drawings. The invention is capable of other embodiments ~r _5_ 21 8141 7 being practiced or carried out in various ways. Also, it is to be understood that the phraseology and terminology employed herein is for the purpose of description and should not be regarded as limiting.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
The present invention is directed to a method and apparatus for treating shallow tumors using pulsed radiation. Treatment of such tumors is problematic, since the outer layers of skin must be penetrated and not harmed~
yet the radiation must get to the underlying tumorous growth sufficient to heat the tumor and cause necrosis. The "effective penetration depth", d, of radiation is a measure of the radiation's ability to penetrate the skin and affect an underlying tumor. It is defined herein as the depth below the surface of the skin at which the radiation fluence reaches 1/e times the magnitude of the radiation fluence on the surface of the skin. Since the effective penetration depth varies with the wavelength of the impinging radiation, tumors at a particular depth can be targeted, and the overlying skin preserved, by selecting and applying particular wavelengths of radiation for tumors at a particular depth.
The effective penetration depth can be estimated by using the effective attenuation coefficient, ~, of the dermis, which takes into account the scattering and absorption of light in tissue. The relation of the effective penetration depth to the effective attenuation coefficient can be estimated as:
d= 1/~.
Following Jacques (S.L. Jacques, Role of Skin optics in Diagnostic and Therapeutic Uses of Lasers, "Lase~s and Dermatology", Springer-Verlag, 1991, pp.1-21), the --6- 2i874~7 effective attenuation coefficient of the dermis can be expressed as follows:
~ = {3 ~ + ~.a~))}
where = attenuation coefficient of dermis ~, = absorption coefficient of dermis ~, = scattering coefficient of dermis, and g = the anisotropy factor, defined as the average cosine of the scattering angle for one scatterin~
event.
Using the above coefficients and factor, a chart has been made of the effective penetration depth in centimeters versus the wavelength of electromagnetic radiation impingin~
upon the skin. This chart is illustrated in FIGURE 1. As FIGURE 1 discloses, the effective penetration depth increases with increasing wavelength, and for wavelengths between 400 nm and 1000 nm varies between 0.03 cm and 0.25 cm. Radiation can penetrate as deeply as 2 mm with a radiation wavelength of 800 nm. The sensitivity of effective penetration depth to wavelength is clear from this chart. For example, d doubles when the wavelength of the impinging radiation increases by a mere 20% (500 to 600 nm~
Because varying the applied radiation wavelength varies the depth of penetration of that radiation, one can control treatment depth by controlling the radiation wavelength.
Hyperthermic treatments also depend upon the length of time radiation is applied to the surface of the skin. The effective depth of tissue heating based on heat conducted from the surface depends upon the conductivity of the skin. The time t, required for a heat wave to penetrate to a depth d, below the surface of the skin can be expres~d as:
~7~ 2 ~ 8 74 1 7 t=d2/a where:
a = the diffusivity of the skin (approximately 3x10-7 m2sec~l) .
Thus, the depth of penetration can be controlled by controlling the time interval over which radiation is applied to the surface of the skin. For example, conducting heat from the surface of a skin throughout a shallow tumor with a thickness of about 1 cm requires about a 5 minute application of radiation to the sur~ace of the skin.
These two modes of heating: conduction from the surface of the skin, and radiant penetration, can be tailored to specific tumors by varying the wavelength and the pulse duration.
A major limitation to the use of radiation sources for therapeutic treatment is the potential tissue damage.
In order to radiate the tumor with the optimum wavelengths of radiation yet not burn tissue, a radiation source is preferably pulsed, thereby providing radiation at wavelengths sufficient to penetrate the tumor to an optimum depth, yet limiting the average energy density during a treatment and preventing the upper layers of the tumor from being overheated.
To provide for the treatment of a wide range of -shallow tumors, the preferred energy density per pulse is between 0.1 and 10 Joules per square centimeter of tumor area. These pulses are preferably repeated at a rate of between 0.1 and 1 Hertz. The number of pulses for treating shallow tumors preferably ranges between 1 and 1000 pulses.
To treat a wide range of tumor sizes, the radiation should be applied to an area of the skin ranging from 0.8 cm2 to 500 cm2.
-8- ~8741 7 It is clear from FIGURE 1 that by irradiating a tumor with selected bands of radiation in the visible and near infrared regions, the tumor can be penetrated to a depth of between 0.05 and 0.25 cm and hyperthermically treated. FIGURE 2 illustrates just such a tumor treatment apparatus 10, having a housing 12 that encloses a radiation source 14, and a reflector 16, and having an opening with a set of optical filters 18,20, and a delivery system 22. A
processor 24 is provided to control radiation source 14 through lamp driver circuit 26, under the control of a program in memory 28.
-- Radiation source 14 is a flashlamp such as a gas filled linear flashlamp Model No. L5568 available from ILC
Typically, a flashlamp's energy is emitted as broad-band incoherent energy in the 300 to 1000 nm wavelength range, which, as FIGURE 1 shows, is well-suited to penetrating tissue to a depth of several millimeters, and thus, for treating shallow tumors.
To treat a tumor, the radiation must be focused and deliverea to the treatment site, and thus reflector 16 and delivery system 22 are provided. Reflector 16 gathers the radiation and directs it toward an opening in the housing. To effectively reflect radiation in the 300 to 1000 nm band, reflector 16 is preferably metallic, typically - aluminum which is-easily machinable and polishable, and has a very high reflectivity in the visible ~nd near infrared ranges of the spectrum. Other bare or coated metals can also be used for this purpose.
Optical filters 18 and neutral density filters 20 are mounted in housing 12 and may be moved into the beam or ;
out of the beam to control the spectrum and intensity of the ~
light. The optical filters may include bandwidth and low _ g ~ i ~ 74 1 7 , cutoff filters in the visible and infrared portions of the spectrum. To limit skin damage, it is desirable to employ W filters to block the W portion of the spectrum, in particular, W filters that cut off the spectral range below 510 nm. For deeper penetration it is preferable to use narrower bandwidth filters. Optical bandwidth filters and the cutoff filters are readily available commercially.
Neutral density filters with varying degrees of filtration can be used to reduce the total fluence transmitted to the skin by blocking the tr~n~ sion of radiation emitted by the radiation source to the treatment site.
The radiation is delivered to the treatment site by delivery system 22, typically an optical fiber or a quartz light guide, although it may be preferable to emit light directly from an opening in the housing. The delivery system should produce fluences on the skin of between 100 mJ/cm2 to 10 J/cm2.
Radiation source 14 is pulsed to provide control of the total fluence, and thus control of tumor and skin heating. To vary the fluence, the delay interval between pulses may be increased or decreased, preferably over a range of a hundred milliseconds to tens of seconds. In this manner, the tumor can be heated at a rate sufficient to allow skin penetration and tumor necrosis, yet not overheat tissue. Total fluence can also be controlled by varying the duration of each pulse over a range of between a hundred microseconds and tens of miiliseconds, to vary the fluence per pulse from a hundred milliJoules to tens of Joules using a flashtube. Total fluence can also be modified by varyin~
the energy per pulse.
Effective penetration depth is dependent on the wavelength of radiation received at the surface of the skin.
-lo- ~ 1 8 7 4 1 7 The present invention provides for changes in wavelength in several ways. Filter 18 can be a low-pass or band-pass filter, thereby blocking selected wavelengths of light.
Varying the power per pulse will also vary the emission spectrum of the radiation source as well.
Processor 24 is provided to control the energy per pulse, the pulse repetition rate, pulse duration rate and the number of pulses per a single treatment. It is connected to radiation source 14 through a lamp driver circuit 26, which is capable of generating power sufficient to trigger radiation source 14. Processor 24 operates under the control of a program stored in memory circuit 28.
The present invention is well suited to treating tumors with a wide variety of sizes. For smaller tumors, a fiber optic delivery system is appropriate. By directing the radiation through a fiber~to the treatment site, small tumors typically on the order of a millimeter or larger in breadth can be treated without endangering the surrolm~;ng tissue. Larger tumors, typically on the order of several square centimeters in projected area, can be treated using a delivery system, that focuses and applies the radiation to a wider treatment site, preferably radiating a 0.8 cm2 area of the treatment site or larger. By appiying the radiation over a larger area, for example 500 cm2, even heating of large tumors can be achieved, reducing the chance of uneven tumor treatment and the risk of damaging tissue.
The present invention has been tested in animal trials and is effective for the treatment of tumors. FIGURE
3 illustrates the inhibition of melanoma B16 growth in mi~e after irradiation in accordance with this invention. The FIGURE 3 chart compares tumor volume versus time for three irradiation levels: a control level (O J/cm2); 90 J/cm2; and 120 J/cm2. Irradiation levels of 90 J/cm2 clearly and significantly delay tumor growth, and an irradiation level of 120 J/cm2 causes the affected tumor to shrink in size.
Extrapolating from these tests, irradiation levels of 200 J/cm2 are believed to provide therapeutic results. The tumor treatment apparatus in these tests applied broad-band radiation in the band from 600 nm to 1000 nm to the tumor.
No apparent tumor response was observed for average radiation power densities below 0.2 W/cm2.
Thus, it should be apparent that there has been provided in accordance with the present invention a method and apparatus for the hyperthermic treatment of tumors that fully satisfies the objectives and advantages set forth above. Although the invention has been described in conjunction with specific embodiments thereof, it is evident that many alternatives, modifications and variations will be apparent to those skilled in the art. Accordingly, it is intended to embrace all such alternatives, modifications and variations that fall within the spirit and broad scope of the appended claims.
- The present invention is directed to a method for the hyperthermic treatment of tumors with electromagnetic radiation including the steps of providing a pulsed radiation output from a radiation source and directing said pulsed radiation output toward a tumor. The radiation may be developed over at least one continuous band of wavelengths, or be generated in the visible and near-infrared band, possibly in a continuous band between 600 an~
1000 nm. In one embodiment, it may include the step of transmitting a broad radiation beam to a pigmented tumor, which might have a cross-sectional area of between 0.8 cm2 and 500 cm2. In another embodiment, it is possible to control the pulse-width of the pulsed radiation output, focus the radiation source for controlling the power density of the pulsed radiation output, or filter and control the spectrum of the pulsed radiation output. In particular, one may focus the pulsed radiation output to a beam having a cross-sectional area of greater than 0.8 cm2.
Alternatively, one may cut off the UV portion of the spectrum. A pulse width in the range of about 100 microseconds to 50 milliseconds may be provided, particularly, one having an energy density at the treatment area of at least 0.2 W/cm2. Alternatively, energy densities of greater than 90 J/c*, 120 J/cm2 per treatment may be provided at the treatment site. A pulse delay of greater than 100 milliseconds or less than 100 seconds may also be provided.
In another embodiment of the invention, an apparatus for the treatment of tumors is provided, including a radiation source producing pulsed radiation at least in the visible and near-infrared wavelengths, a delivery system _4_ 21 8741 7 near the radiation source for focusing and directing the radiation to a treatment site, and a filtering system restricting the radiation to visible and near-infrared wavelengths. Alternatively, the radiation source may produce pulsed radiation in a broad band, or over at least - one continuous range of wavelengths. This may be focused in a beam of at least 0.8 cm2. The radiation may be restricted to a band between 300 and 1000 nm, or may be W blocked by a filter. The radiation pulses may have a duration of between 100 ~secs and 100 msecs, and may be spaced from 100 msecs to 100 secs apart. In addition, they may be delivered to the treatment area with a radiation-density of greater than 0.2 W/cm2, 90 Jtcm2, or 120 Jlcm2. The radiation may also be limited to a radiation density of less than 200 J/cm2.
Other principal features and advantages of the invention will become apparent to those skilled in the art upon review of the following drawings, the detailed description and the appended claims.
BRIEF DESCRIPTION OF THE DRAWINGS
~ IG~RE 1 is a graph of radiation tissue penetration versus radiation wavelength;
FIG~RE 2 is a cross-sectional view of tumor treatment -device according to the present invention; and - FIG~RE 3 is a graph of treatment results using the FIGURE 2 tumor treatment device.
- Before explaining at least one embodiment of the invention in detail it is to be understood that the invention is not limited in its application to the details of construction and the arrangement of the components set forth in the following description or illustrated in the drawings. The invention is capable of other embodiments ~r _5_ 21 8141 7 being practiced or carried out in various ways. Also, it is to be understood that the phraseology and terminology employed herein is for the purpose of description and should not be regarded as limiting.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
The present invention is directed to a method and apparatus for treating shallow tumors using pulsed radiation. Treatment of such tumors is problematic, since the outer layers of skin must be penetrated and not harmed~
yet the radiation must get to the underlying tumorous growth sufficient to heat the tumor and cause necrosis. The "effective penetration depth", d, of radiation is a measure of the radiation's ability to penetrate the skin and affect an underlying tumor. It is defined herein as the depth below the surface of the skin at which the radiation fluence reaches 1/e times the magnitude of the radiation fluence on the surface of the skin. Since the effective penetration depth varies with the wavelength of the impinging radiation, tumors at a particular depth can be targeted, and the overlying skin preserved, by selecting and applying particular wavelengths of radiation for tumors at a particular depth.
The effective penetration depth can be estimated by using the effective attenuation coefficient, ~, of the dermis, which takes into account the scattering and absorption of light in tissue. The relation of the effective penetration depth to the effective attenuation coefficient can be estimated as:
d= 1/~.
Following Jacques (S.L. Jacques, Role of Skin optics in Diagnostic and Therapeutic Uses of Lasers, "Lase~s and Dermatology", Springer-Verlag, 1991, pp.1-21), the --6- 2i874~7 effective attenuation coefficient of the dermis can be expressed as follows:
~ = {3 ~ + ~.a~))}
where = attenuation coefficient of dermis ~, = absorption coefficient of dermis ~, = scattering coefficient of dermis, and g = the anisotropy factor, defined as the average cosine of the scattering angle for one scatterin~
event.
Using the above coefficients and factor, a chart has been made of the effective penetration depth in centimeters versus the wavelength of electromagnetic radiation impingin~
upon the skin. This chart is illustrated in FIGURE 1. As FIGURE 1 discloses, the effective penetration depth increases with increasing wavelength, and for wavelengths between 400 nm and 1000 nm varies between 0.03 cm and 0.25 cm. Radiation can penetrate as deeply as 2 mm with a radiation wavelength of 800 nm. The sensitivity of effective penetration depth to wavelength is clear from this chart. For example, d doubles when the wavelength of the impinging radiation increases by a mere 20% (500 to 600 nm~
Because varying the applied radiation wavelength varies the depth of penetration of that radiation, one can control treatment depth by controlling the radiation wavelength.
Hyperthermic treatments also depend upon the length of time radiation is applied to the surface of the skin. The effective depth of tissue heating based on heat conducted from the surface depends upon the conductivity of the skin. The time t, required for a heat wave to penetrate to a depth d, below the surface of the skin can be expres~d as:
~7~ 2 ~ 8 74 1 7 t=d2/a where:
a = the diffusivity of the skin (approximately 3x10-7 m2sec~l) .
Thus, the depth of penetration can be controlled by controlling the time interval over which radiation is applied to the surface of the skin. For example, conducting heat from the surface of a skin throughout a shallow tumor with a thickness of about 1 cm requires about a 5 minute application of radiation to the sur~ace of the skin.
These two modes of heating: conduction from the surface of the skin, and radiant penetration, can be tailored to specific tumors by varying the wavelength and the pulse duration.
A major limitation to the use of radiation sources for therapeutic treatment is the potential tissue damage.
In order to radiate the tumor with the optimum wavelengths of radiation yet not burn tissue, a radiation source is preferably pulsed, thereby providing radiation at wavelengths sufficient to penetrate the tumor to an optimum depth, yet limiting the average energy density during a treatment and preventing the upper layers of the tumor from being overheated.
To provide for the treatment of a wide range of -shallow tumors, the preferred energy density per pulse is between 0.1 and 10 Joules per square centimeter of tumor area. These pulses are preferably repeated at a rate of between 0.1 and 1 Hertz. The number of pulses for treating shallow tumors preferably ranges between 1 and 1000 pulses.
To treat a wide range of tumor sizes, the radiation should be applied to an area of the skin ranging from 0.8 cm2 to 500 cm2.
-8- ~8741 7 It is clear from FIGURE 1 that by irradiating a tumor with selected bands of radiation in the visible and near infrared regions, the tumor can be penetrated to a depth of between 0.05 and 0.25 cm and hyperthermically treated. FIGURE 2 illustrates just such a tumor treatment apparatus 10, having a housing 12 that encloses a radiation source 14, and a reflector 16, and having an opening with a set of optical filters 18,20, and a delivery system 22. A
processor 24 is provided to control radiation source 14 through lamp driver circuit 26, under the control of a program in memory 28.
-- Radiation source 14 is a flashlamp such as a gas filled linear flashlamp Model No. L5568 available from ILC
Typically, a flashlamp's energy is emitted as broad-band incoherent energy in the 300 to 1000 nm wavelength range, which, as FIGURE 1 shows, is well-suited to penetrating tissue to a depth of several millimeters, and thus, for treating shallow tumors.
To treat a tumor, the radiation must be focused and deliverea to the treatment site, and thus reflector 16 and delivery system 22 are provided. Reflector 16 gathers the radiation and directs it toward an opening in the housing. To effectively reflect radiation in the 300 to 1000 nm band, reflector 16 is preferably metallic, typically - aluminum which is-easily machinable and polishable, and has a very high reflectivity in the visible ~nd near infrared ranges of the spectrum. Other bare or coated metals can also be used for this purpose.
Optical filters 18 and neutral density filters 20 are mounted in housing 12 and may be moved into the beam or ;
out of the beam to control the spectrum and intensity of the ~
light. The optical filters may include bandwidth and low _ g ~ i ~ 74 1 7 , cutoff filters in the visible and infrared portions of the spectrum. To limit skin damage, it is desirable to employ W filters to block the W portion of the spectrum, in particular, W filters that cut off the spectral range below 510 nm. For deeper penetration it is preferable to use narrower bandwidth filters. Optical bandwidth filters and the cutoff filters are readily available commercially.
Neutral density filters with varying degrees of filtration can be used to reduce the total fluence transmitted to the skin by blocking the tr~n~ sion of radiation emitted by the radiation source to the treatment site.
The radiation is delivered to the treatment site by delivery system 22, typically an optical fiber or a quartz light guide, although it may be preferable to emit light directly from an opening in the housing. The delivery system should produce fluences on the skin of between 100 mJ/cm2 to 10 J/cm2.
Radiation source 14 is pulsed to provide control of the total fluence, and thus control of tumor and skin heating. To vary the fluence, the delay interval between pulses may be increased or decreased, preferably over a range of a hundred milliseconds to tens of seconds. In this manner, the tumor can be heated at a rate sufficient to allow skin penetration and tumor necrosis, yet not overheat tissue. Total fluence can also be controlled by varying the duration of each pulse over a range of between a hundred microseconds and tens of miiliseconds, to vary the fluence per pulse from a hundred milliJoules to tens of Joules using a flashtube. Total fluence can also be modified by varyin~
the energy per pulse.
Effective penetration depth is dependent on the wavelength of radiation received at the surface of the skin.
-lo- ~ 1 8 7 4 1 7 The present invention provides for changes in wavelength in several ways. Filter 18 can be a low-pass or band-pass filter, thereby blocking selected wavelengths of light.
Varying the power per pulse will also vary the emission spectrum of the radiation source as well.
Processor 24 is provided to control the energy per pulse, the pulse repetition rate, pulse duration rate and the number of pulses per a single treatment. It is connected to radiation source 14 through a lamp driver circuit 26, which is capable of generating power sufficient to trigger radiation source 14. Processor 24 operates under the control of a program stored in memory circuit 28.
The present invention is well suited to treating tumors with a wide variety of sizes. For smaller tumors, a fiber optic delivery system is appropriate. By directing the radiation through a fiber~to the treatment site, small tumors typically on the order of a millimeter or larger in breadth can be treated without endangering the surrolm~;ng tissue. Larger tumors, typically on the order of several square centimeters in projected area, can be treated using a delivery system, that focuses and applies the radiation to a wider treatment site, preferably radiating a 0.8 cm2 area of the treatment site or larger. By appiying the radiation over a larger area, for example 500 cm2, even heating of large tumors can be achieved, reducing the chance of uneven tumor treatment and the risk of damaging tissue.
The present invention has been tested in animal trials and is effective for the treatment of tumors. FIGURE
3 illustrates the inhibition of melanoma B16 growth in mi~e after irradiation in accordance with this invention. The FIGURE 3 chart compares tumor volume versus time for three irradiation levels: a control level (O J/cm2); 90 J/cm2; and 120 J/cm2. Irradiation levels of 90 J/cm2 clearly and significantly delay tumor growth, and an irradiation level of 120 J/cm2 causes the affected tumor to shrink in size.
Extrapolating from these tests, irradiation levels of 200 J/cm2 are believed to provide therapeutic results. The tumor treatment apparatus in these tests applied broad-band radiation in the band from 600 nm to 1000 nm to the tumor.
No apparent tumor response was observed for average radiation power densities below 0.2 W/cm2.
Thus, it should be apparent that there has been provided in accordance with the present invention a method and apparatus for the hyperthermic treatment of tumors that fully satisfies the objectives and advantages set forth above. Although the invention has been described in conjunction with specific embodiments thereof, it is evident that many alternatives, modifications and variations will be apparent to those skilled in the art. Accordingly, it is intended to embrace all such alternatives, modifications and variations that fall within the spirit and broad scope of the appended claims.
Claims (27)
1. A method for the hyperthermic treatment of tumors with electromagnetic radiation comprising the steps of:
providing pulsed radiation output from a radiation source; and directing said pulsed radiation output toward a tumor.
providing pulsed radiation output from a radiation source; and directing said pulsed radiation output toward a tumor.
2. The method of claim 1, wherein the step of providing a pulsed radiation output includes the step of generating the pulsed radiation output over at least one continuous band of wavelengths.
3. The method of claim 1, wherein the step of providing a pulsed radiation output includes the step of generating the pulsed radiation output in a visible and near-infrared band.
4. The method of claim 3, wherein the step of generating the pulsed radiation output in a visible and near-infrared band includes the step of generating a continuous band of wavelengths between the wavelengths of 600 nm and 1000 nm.
5. The method of claim 2 wherein the step of directing said pulsed radiation output at a tumor including the step of transmitting a broad radiation beam to a pigmented tumor.
6. The method of claim 5, wherein the broad radiation beam has a cross-sectional area of between 0.8 cm2 to 500 cm2.
7. The method of claim 2 further comprising the steps of:
controlling the pulse-width of said pulsed radiation output;
focusing said radiation source for controlling the power density of said pulsed radiation output; and filtering and controlling the spectrum of said pulsed radiation output.
controlling the pulse-width of said pulsed radiation output;
focusing said radiation source for controlling the power density of said pulsed radiation output; and filtering and controlling the spectrum of said pulsed radiation output.
8. The method of claim 7, wherein the step of focusing said radiation source includes the step of focusing the pulsed radiation output to a beam having a cross-sectional area of greater than 0.8 cm.
9. The method of claim 7 wherein the step of filtering and controlling the spectrum includes the step of cutting off the UV portion of the spectrum.
10. The method of claim 7 wherein said step of controlling the pulse width includes the step of providing a pulse width in the range of about 100 microseconds to 50 milliseconds with energy density of the pulsed radiation output at the treatment area of at least 0.2 W/cm.
11. The method of claim 10 wherein the energy density of the pulsed radiation output at the treatment area is greater than 90 J/cm per treatment.
12. The method of claim 10 wherein the energy density of the pulsed radiation output at the treatment area is greater than 120 J/cm per treatment.
13. The method of claim 10 further including the step of providing a pulse delay of greater than 100 milliseconds.
14. The method of claim 13 wherein the step of providing radiation delays includes the step of limiting the delay duration to less that 100 seconds.
15. An apparatus for the hyperthermic treatment of tumors comprising:
a radiation source adapted to produce pulsed radiation output at least in the visible and near-infrared range of wavelengths;
a delivery system proximal to the radiation source and adapted to focus and direct the pulsed radiation output to a dermal treatment site; and a filtering system adapted to restrict the pulsed radiation output to bands in the visible and near-infrared range of wavelengths.
a radiation source adapted to produce pulsed radiation output at least in the visible and near-infrared range of wavelengths;
a delivery system proximal to the radiation source and adapted to focus and direct the pulsed radiation output to a dermal treatment site; and a filtering system adapted to restrict the pulsed radiation output to bands in the visible and near-infrared range of wavelengths.
16. The apparatus of claim 15, wherein said radiation source is further adapted to produce said pulsed radiation output in a broad band.
17. The apparatus of claim 15, wherein the radiation source is adapted to produce said pulsed radiation output over at least one continuous band of wavelengths.
18. The apparatus of claim 17 wherein the delivery system is adapted to focus the pulsed radiation output to a beam having a cross-sectional area of at least 0.8 cm.
19. The apparatus of claim 18, wherein the filtering system is adapted to restricting the pulsed radiation output to a band between 300 and 1000 nm.
20. The apparatus of claim 19 wherein the filtering system includes a filter adapted to block UV
wavelengths.
wavelengths.
21. The apparatus of claim 17, wherein the pulsed radiation source is adapted to provide a pulse duration between 100 microseconds and 100 milliseconds.
22. The apparatus of claim 21, wherein the pulsed radiation source is adapted to provide a pulse delay of between 100 milliseconds and 50 seconds between pulses.
23. The apparatus of claim 22, wherein the delivery system is adapted to deliver the pulsed radiation output to the treatment area with a radiation density of greater than 0.2 W/cm.
24. The apparatus of claim 23, wherein the delivery system is adapted to deliver the pulsed radiation output to the treatment area with a radiation density of greater than 90 J/cm.
25. The apparatus of claim 24, wherein the delivery system is adapted to deliver pulsed radiation output to the treatment area with a radiation density of less than 200 J/cm.
26. The apparatus of claim 25, wherein the delivery system is adapted to deliver pulsed radiation output to the treatment area with a radiation density of greater than 120 J/cm.
27. The apparatus of claim 22 further including a processor adapted to control the pulse duration and pulse delay.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/536,985 US5776175A (en) | 1995-09-29 | 1995-09-29 | Method and apparatus for treatment of cancer using pulsed electromagnetic radiation |
US08/536,985 | 1995-09-29 |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2187417A1 true CA2187417A1 (en) | 1997-03-30 |
Family
ID=24140718
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002187417A Abandoned CA2187417A1 (en) | 1995-09-29 | 1996-10-08 | Method and apparatus for treatment of cancer using electromagnetic radiation |
Country Status (7)
Country | Link |
---|---|
US (1) | US5776175A (en) |
EP (1) | EP0765673A3 (en) |
JP (1) | JPH09103509A (en) |
KR (1) | KR970014786A (en) |
AU (1) | AU726249B2 (en) |
BR (1) | BR9603841A (en) |
CA (1) | CA2187417A1 (en) |
Families Citing this family (70)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6350276B1 (en) | 1996-01-05 | 2002-02-26 | Thermage, Inc. | Tissue remodeling apparatus containing cooling fluid |
US7452358B2 (en) * | 1996-01-05 | 2008-11-18 | Thermage, Inc. | RF electrode assembly for handpiece |
GB9618051D0 (en) * | 1996-08-29 | 1996-10-09 | Sls Wales Ltd | Wrinkle removal |
US8182473B2 (en) | 1999-01-08 | 2012-05-22 | Palomar Medical Technologies | Cooling system for a photocosmetic device |
US6508813B1 (en) | 1996-12-02 | 2003-01-21 | Palomar Medical Technologies, Inc. | System for electromagnetic radiation dermatology and head for use therewith |
US6517532B1 (en) | 1997-05-15 | 2003-02-11 | Palomar Medical Technologies, Inc. | Light energy delivery head |
US6653618B2 (en) | 2000-04-28 | 2003-11-25 | Palomar Medical Technologies, Inc. | Contact detecting method and apparatus for an optical radiation handpiece |
US6317624B1 (en) | 1997-05-05 | 2001-11-13 | The General Hospital Corporation | Apparatus and method for demarcating tumors |
ES2226133T3 (en) | 1997-05-15 | 2005-03-16 | Palomar Medical Technologies, Inc. | DERMATOLOGICAL TREATMENT DEVICE. |
EP0885629A3 (en) | 1997-06-16 | 1999-07-21 | Danish Dermatologic Development A/S | Light pulse generating apparatus and cosmetic and therapeutic phototreatment |
ATE446122T1 (en) * | 1998-01-15 | 2009-11-15 | Regenesis Biomedical Inc | IMPROVED APPARATUS FOR TREATMENT USING PULSE ELECTROMAGNETIC ENERGY |
ES2403359T3 (en) | 1998-03-27 | 2013-05-17 | The General Hospital Corporation | Procedure and apparatus for the selective determination of lipid rich tissues |
GB2339538A (en) * | 1998-07-14 | 2000-02-02 | Robert Kenneth Hackett | Colonicure |
US6595986B2 (en) | 1998-10-15 | 2003-07-22 | Stephen Almeida | Multiple pulse photo-dermatological device |
US6454789B1 (en) * | 1999-01-15 | 2002-09-24 | Light Science Corporation | Patient portable device for photodynamic therapy |
JP2002534218A (en) * | 1999-01-15 | 2002-10-15 | ライト サイエンシーズ コーポレイション | Non-invasive vascular therapy |
US6602274B1 (en) | 1999-01-15 | 2003-08-05 | Light Sciences Corporation | Targeted transcutaneous cancer therapy |
DE19912992A1 (en) * | 1999-03-23 | 2000-09-28 | Romberg Hans | Laser irradiation method for medical or cosmetic purposes, or for use on animals, plants or cell culture; involves using laser diode, with pulse characteristics varied to alter effective illumination |
US6326177B1 (en) | 1999-08-04 | 2001-12-04 | Eastern Virginia Medical School Of The Medical College Of Hampton Roads | Method and apparatus for intracellular electro-manipulation |
EP1267935A2 (en) | 2000-01-12 | 2003-01-02 | Light Sciences Corporation | Novel treatment for eye disease |
RU2165743C1 (en) * | 2000-09-12 | 2001-04-27 | Хомченко Владимир Валентинович | Method for performing blood vessel laser coagulation |
US20030130649A1 (en) * | 2000-12-15 | 2003-07-10 | Murray Steven C. | Method and system for treatment of benign prostatic hypertrophy (BPH) |
US6986764B2 (en) * | 2000-12-15 | 2006-01-17 | Laserscope | Method and system for photoselective vaporization of the prostate, and other tissue |
US6554824B2 (en) * | 2000-12-15 | 2003-04-29 | Laserscope | Methods for laser treatment of soft tissue |
US6723090B2 (en) | 2001-07-02 | 2004-04-20 | Palomar Medical Technologies, Inc. | Fiber laser device for medical/cosmetic procedures |
US6706040B2 (en) | 2001-11-23 | 2004-03-16 | Medlennium Technologies, Inc. | Invasive therapeutic probe |
WO2003047684A2 (en) * | 2001-12-04 | 2003-06-12 | University Of Southern California | Method for intracellular modifications within living cells using pulsed electric fields |
WO2003072189A2 (en) * | 2002-02-22 | 2003-09-04 | Laserscope | Method and system for photoselective vaporization for gynecological treatments |
WO2004000098A2 (en) | 2002-06-19 | 2003-12-31 | Palomar Medical Technologies, Inc. | Method and apparatus for treatment of cutaneous and subcutaneous conditions |
US6824555B1 (en) | 2002-07-22 | 2004-11-30 | Uop Llc | Combustion needle for medical applications |
US6960225B1 (en) | 2002-07-22 | 2005-11-01 | Uop Llc | Medical applications using microcombustion |
AU2003284972B2 (en) | 2002-10-23 | 2009-09-10 | Palomar Medical Technologies, Inc. | Phototreatment device for use with coolants and topical substances |
US20050059153A1 (en) * | 2003-01-22 | 2005-03-17 | George Frank R. | Electromagnetic activation of gene expression and cell growth |
US20050177141A1 (en) * | 2003-01-27 | 2005-08-11 | Davenport Scott A. | System and method for dermatological treatment gas discharge lamp with controllable current density |
US20040147985A1 (en) * | 2003-01-27 | 2004-07-29 | Altus Medical, Inc. | Dermatological treatment flashlamp device and method |
US7703458B2 (en) * | 2003-02-21 | 2010-04-27 | Cutera, Inc. | Methods and devices for non-ablative laser treatment of dermatologic conditions |
FR2864903B1 (en) * | 2004-01-14 | 2006-09-15 | Optical System Res For Industr | APPARATUS FOR THE TREATMENT, IN PARTICULAR BY LASER, OF A CANCER OR PRECANCEROUS CONDITION |
US7313155B1 (en) * | 2004-02-12 | 2007-12-25 | Liyue Mu | High power Q-switched laser for soft tissue ablation |
US20050209331A1 (en) * | 2004-03-22 | 2005-09-22 | Syneron Medical Ltd. | Method of treatment of skin |
US20050209330A1 (en) * | 2004-03-22 | 2005-09-22 | Syneron Medical Ltd. | Method of treatment of skin |
US7496397B2 (en) * | 2004-05-06 | 2009-02-24 | Boston Scientific Scimed, Inc. | Intravascular antenna |
US8137340B2 (en) * | 2004-06-23 | 2012-03-20 | Applied Harmonics Corporation | Apparatus and method for soft tissue ablation employing high power diode-pumped laser |
WO2006020605A2 (en) * | 2004-08-10 | 2006-02-23 | The Regents Of The University Of California | Device and method for the delivery and/or elimination of compounds in tissue |
US20060094781A1 (en) * | 2004-11-04 | 2006-05-04 | Syneron Medical Ltd. | Method of treating extracellular matrix |
US7856985B2 (en) | 2005-04-22 | 2010-12-28 | Cynosure, Inc. | Method of treatment body tissue using a non-uniform laser beam |
US7559275B1 (en) * | 2005-05-26 | 2009-07-14 | Dole Fresh Vegetables, Inc. | Top and tail trimming system for leafy vegetables |
US7862556B2 (en) * | 2005-06-17 | 2011-01-04 | Applied Harmonics Corporation | Surgical system that ablates soft tissue |
JP2007029603A (en) * | 2005-07-29 | 2007-02-08 | Fujinon Corp | Optical diagnostic treatment apparatus |
JP2009509140A (en) | 2005-09-15 | 2009-03-05 | パロマー・メデイカル・テクノロジーズ・インコーポレーテツド | Skin optical determination device |
US20090054763A1 (en) * | 2006-01-19 | 2009-02-26 | The Regents Of The University Of Michigan | System and method for spectroscopic photoacoustic tomography |
WO2007084981A2 (en) * | 2006-01-19 | 2007-07-26 | The Regents Of The University Of Michigan | System and method for photoacoustic imaging and monitoring of laser therapy |
US20070250051A1 (en) * | 2006-04-25 | 2007-10-25 | Gaston Kerry R | Heating via microwave and millimeter-wave transmission using a hypodermic needle |
US8460280B2 (en) * | 2006-04-28 | 2013-06-11 | Cutera, Inc. | Localized flashlamp skin treatments |
US20080086118A1 (en) * | 2006-05-17 | 2008-04-10 | Applied Harmonics Corporation | Apparatus and method for diode-pumped laser ablation of soft tissue |
US20080033412A1 (en) * | 2006-08-01 | 2008-02-07 | Harry Thomas Whelan | System and method for convergent light therapy having controllable dosimetry |
US7586957B2 (en) | 2006-08-02 | 2009-09-08 | Cynosure, Inc | Picosecond laser apparatus and methods for its operation and use |
US20080173093A1 (en) * | 2007-01-18 | 2008-07-24 | The Regents Of The University Of Michigan | System and method for photoacoustic tomography of joints |
WO2008103982A2 (en) * | 2007-02-23 | 2008-08-28 | The Regents Of The University Of Michigan | System and method for monitoring photodynamic therapy |
US20080287940A1 (en) * | 2007-05-14 | 2008-11-20 | Hunter Lowell D | Fiber Pole Tip |
US8419718B2 (en) * | 2007-05-15 | 2013-04-16 | Ams Research Corporation | Laser handle and fiber guard |
US8920409B2 (en) * | 2007-10-04 | 2014-12-30 | Cutera, Inc. | System and method for dermatological lesion treatment using gas discharge lamp with controllable current density |
US9504824B2 (en) | 2009-06-23 | 2016-11-29 | Board Of Regents, The University Of Texas System | Noninvasive therapies in the absence or presence of exogenous particulate agents |
US9919168B2 (en) | 2009-07-23 | 2018-03-20 | Palomar Medical Technologies, Inc. | Method for improvement of cellulite appearance |
US8549996B2 (en) | 2010-05-28 | 2013-10-08 | Dole Fresh Vegetables, Inc. | System for topping and tailing lettuce heads using a camera-guided servo-controlled water knife |
KR102342629B1 (en) | 2012-04-18 | 2021-12-22 | 싸이노슈어, 엘엘씨 | Picosecond laser apparatus and methods for treating target tissues with same |
US20140271453A1 (en) | 2013-03-14 | 2014-09-18 | Abbott Laboratories | Methods for the early detection of lung cancer |
US10285757B2 (en) | 2013-03-15 | 2019-05-14 | Cynosure, Llc | Picosecond optical radiation systems and methods of use |
TWI461203B (en) * | 2013-07-04 | 2014-11-21 | Academia Sinica | Tumor vessel embolizing agent and use of au nanoparticles |
AU2017368332A1 (en) | 2016-12-03 | 2019-06-13 | Juno Therapeutics, Inc. | Methods for modulation of CAR-T cells |
KR102627248B1 (en) | 2018-02-26 | 2024-01-19 | 싸이노슈어, 엘엘씨 | Q-switched cavity dumping subnanosecond laser |
Family Cites Families (26)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2609273A1 (en) * | 1976-03-05 | 1977-09-08 | Mutzhas Maximilian F | IRRADIATION DEVICE WITH ULTRAVIOLET RADIATION SOURCE |
US4022534A (en) * | 1976-03-23 | 1977-05-10 | Kollmorgen Corporation | Reflectometer optical system |
HU186081B (en) * | 1981-09-02 | 1985-05-28 | Fenyo Marta | Process and apparatus for stimulating healing of pathologic points on the surface of the body first of all of wounds, ulcera and other epithelial lesions |
US4784135A (en) * | 1982-12-09 | 1988-11-15 | International Business Machines Corporation | Far ultraviolet surgical and dental procedures |
US4608978A (en) * | 1983-09-26 | 1986-09-02 | Carol Block Limited | Method and apparatus for photoepiltion |
US5226430A (en) * | 1984-10-24 | 1993-07-13 | The Beth Israel Hospital | Method for angioplasty |
ATE51730T1 (en) * | 1984-10-25 | 1990-04-15 | Candela Laser Corp | TUNABLE LONG-PULSE DYE LASER. |
US4862886A (en) * | 1985-05-08 | 1989-09-05 | Summit Technology Inc. | Laser angioplasty |
US4757431A (en) * | 1986-07-01 | 1988-07-12 | Laser Media | Off-axis application of concave spherical reflectors as condensing and collecting optics |
US4926861A (en) * | 1987-10-08 | 1990-05-22 | Harrier Inc. | Method for in vivo treatment of tumorous tissues on body surfaces |
US5259380A (en) * | 1987-11-04 | 1993-11-09 | Amcor Electronics, Ltd. | Light therapy system |
US4930504A (en) * | 1987-11-13 | 1990-06-05 | Diamantopoulos Costas A | Device for biostimulation of tissue and method for treatment of tissue |
DE3906860A1 (en) * | 1988-03-08 | 1989-09-28 | Fraunhofer Ges Forschung | Device for producing an angiography |
US5161526A (en) * | 1989-04-04 | 1992-11-10 | Hellwing Isak A | Method of treating of bleeding in hemophiliacs |
US4950880A (en) * | 1989-07-28 | 1990-08-21 | Recon/Optical, Inc. | Synthetic aperture optical imaging system |
SE465953B (en) * | 1990-04-09 | 1991-11-25 | Morgan Gustafsson | DEVICE FOR TREATMENT OF UNDESECTED EXTERNAL ACCOMMODATIONS |
US5207671A (en) * | 1991-04-02 | 1993-05-04 | Franken Peter A | Laser debridement of wounds |
US5217455A (en) * | 1991-08-12 | 1993-06-08 | Tan Oon T | Laser treatment method for removing pigmentations, lesions, and abnormalities from the skin of a living human |
IL100181A (en) * | 1991-11-28 | 1995-10-31 | Dimotech Ltd | Apparatus for the treatment of skin wounds |
US5344418A (en) * | 1991-12-12 | 1994-09-06 | Shahriar Ghaffari | Optical system for treatment of vascular lesions |
IL100545A (en) * | 1991-12-29 | 1995-03-15 | Dimotech Ltd | Apparatus for photodynamic therapy treatment |
US5405368A (en) * | 1992-10-20 | 1995-04-11 | Esc Inc. | Method and apparatus for therapeutic electromagnetic treatment |
CA2093055C (en) * | 1992-04-09 | 2002-02-19 | Shimon Eckhouse | Method and apparatus for therapeutic electromagnetic treatment |
GB2272278B (en) * | 1992-10-23 | 1997-04-09 | Cancer Res Campaign Tech | Light source |
US5386837A (en) * | 1993-02-01 | 1995-02-07 | Mmtc, Inc. | Method for enhancing delivery of chemotherapy employing high-frequency force fields |
US5368031A (en) * | 1993-08-29 | 1994-11-29 | General Electric Company | Magnetic resonance surgery using heat waves produced with a laser fiber |
-
1995
- 1995-09-29 US US08/536,985 patent/US5776175A/en not_active Expired - Lifetime
-
1996
- 1996-09-04 AU AU64464/96A patent/AU726249B2/en not_active Ceased
- 1996-09-20 BR BR9603841A patent/BR9603841A/en not_active Application Discontinuation
- 1996-09-23 KR KR1019960043483A patent/KR970014786A/en not_active Application Discontinuation
- 1996-09-23 EP EP96306916A patent/EP0765673A3/en not_active Withdrawn
- 1996-09-27 JP JP8256706A patent/JPH09103509A/en active Pending
- 1996-10-08 CA CA002187417A patent/CA2187417A1/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
US5776175A (en) | 1998-07-07 |
EP0765673A2 (en) | 1997-04-02 |
AU6446496A (en) | 1997-04-10 |
BR9603841A (en) | 1998-06-02 |
JPH09103509A (en) | 1997-04-22 |
EP0765673A3 (en) | 1999-04-21 |
KR970014786A (en) | 1997-04-28 |
AU726249B2 (en) | 2000-11-02 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US5776175A (en) | Method and apparatus for treatment of cancer using pulsed electromagnetic radiation | |
US5836999A (en) | Method and apparatus for treating psoriasis using pulsed electromagnetic radiation | |
US5643334A (en) | Method and apparatus for the diagnostic and composite pulsed heating and photodynamic therapy treatment | |
US5527350A (en) | Pulsed infrared laser treatment of psoriasis | |
US5964749A (en) | Method and apparatus for skin rejuvenation and wrinkle smoothing | |
Peavy | Lasers and laser–tissue interaction | |
US6235015B1 (en) | Method and apparatus for selective hair depilation using a scanned beam of light at 600 to 1000 nm | |
US7618414B2 (en) | Tissue treatment system | |
Herd et al. | Basic laser principles | |
US7108689B2 (en) | Method and apparatus for electromagnetic treatment of the skin, including hair depilation | |
CA2195294C (en) | Method and apparatus for depilation using pulsed electromagnetic radiation | |
US6666856B2 (en) | Hair removal device and method | |
US6829260B2 (en) | Multipulse dye laser | |
US20130096546A1 (en) | Non-uniform beam optical treatment methods and systems | |
EP0172490A1 (en) | Laser system for providing target specific energy deposition and damage | |
US6364872B1 (en) | Multipulse dye laser | |
US20040034397A1 (en) | Method and apparatus for treating skin disorders using a short pulsed incoherent light | |
WO1999032193A1 (en) | Apparatus for therapeutic electromagnetic treatment | |
Exley | Investigation of photothermal processes in dermatological lesions | |
Miller | Edward Victor Ross | |
Verkruysse et al. | Port-wine stain treatment is wavelength independent in the range 488–620 nm using 200-ms pulses | |
Sliney | Appropriate radiometric quantities in laser dosimetry | |
Goldberg | Flashlamp-excited dye laser therapy for treatment of cutaneous vascular lesions | |
EP1520546A1 (en) | Method of laser depilation |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
FZDE | Discontinued |
Effective date: 20031008 |