Patent Application
20080033412
The concept of an electromagnetic spectrum is an attempt to formalize and organize the notion of energy transmission across space and time, either via electromagnetic waves which serve to propagate energy, or equivalently, through transmission of particle-like photons. Wave-particle duality, a fundamental concept of quantum physics, ensures that these two views are, in fact, self-consistent and equivalent.
The wave/photon model of electromagnetic energy transmission incorporates the idea that energy is quantisized and is proportional to the frequency of the wave “packet” or photon. The energy carried by a single photon ‘particle’ in a vacuum is given by E=hv, where v is the frequency of the photon (or associated electromagnetic wave), and h is Planck's constant, given by 6.626×10-34 joule-seconds. Alternatively, the energy E can be written as E=hc/λ, where λ is the wavelength of the photon/wave and c is the velocity of light in a vacuum.
The portion of the electromagnetic spectrum for which photons possess wavelengths between 400 and 700 nanometers (nm) is of particular interest. Photons in this range possess sufficient energy to reach the posterior lining of the human eye, where they release their energy to rhodopsin molecules, triggering a cascade of biochemical reactions which ultimately results in the human perception of light. Indeed, the properties of photons in this so-called “visible region” of the electromagnetic spectrum and the biochemical reactions triggered by these photons are well-characterized and well-understood.
In contrast, there exists only a rudimentary understanding of analogous biochemical processes which are triggered in human cells by photons of ‘light’ radiation in the wavelength range 600-900 nm or “near-infrared” and lower “infrared” regions. One interaction which has come under intense scrutiny recently is the interaction of visible/near-infrared photons with mitochondrial proteins, such as cytochrome c oxidase. As will be described below with respect to the listed Examples, the energy exchange between incident photons and molecules of cytochrome c oxidase can affect significant, measurable, and reproducible changes at the cell, tissue, organ, and system level. Furthermore, these changes can, under certain circumstances, ameliorate pathological states of health, with beneficial results.
Referring to
As will be described below with respect to the Examples, evidence has demonstrated that neurons exposed to light in the near-infrared spectrum can render such neurons more resistant to oxidative stress. Such types of stress are at the core of many neurodegenerative disorders such as Parkinson's disease and Alzheimer's disease. As will be described, the present invention provides a system and method for photobiomodulation by light in the red to near-infrared range (630-880 nm) and can improve recovery from ischemic injury in the heart, attenuate degeneration in the injured optic nerve, and protect against mitochondrial dysfunction in the retina.
As will be described, the present invention includes a near-infrared (IR) device designed to maximize internal tissue light dose (e.g., as applied to the brain), non-invasively, by convergence of multiple surface beams. Additionally, as will be described, the system is capable of delivering adequate doses of near-IR light evenly into the major internal organs of the body. In particular, the system is capable of delivering sufficient near-IR light deep into targeted tissues.
Mechanistic studies have shown that far-red to near-infrared light interacts with the enzyme cytochrome oxidase in mitochondria triggering signaling mechanisms which result in improved energy production, antioxidant protection, and cell survival. To this end, photobiomodulation will augment mitochondrial function and stimulate antioxidant protective pathways in cellular and animal models of Parkinson's Disease. Hence, as will be described below, the present invention is designed to therapeutically and non-invasively treat a targeted area of a patient to manifestly alter the course of a disease early on in the course of a development.
The present invention recognizes that nitric oxide is a molecule that can be used a signal of intercellular activity or change. For example, nitric oxide has a role in the control of blood flow and blood pressure via activation of the heme enzyme, soluble guanylate cyclase. Furthermore, the present invention recognizes that nitric oxide targets the mitochondrial oxygen-consuming heme/copper enzyme, cytochrome c oxidase.
As will be described, the present invention provides a system and method for identifying a minimal or minimum dose of near-IR light delivered to a target area to effectuate a desired biochemical state of cytochrome c oxidase using feedback from nitric oxide and dynamically controlling a dose of near-IR light delivered to the target area.
Referring now to
In particular, referring now to
To control the position of the patient 26, the patient table 20 is used that includes a patent support bed 32 that is dynamically controllable through a bed motor controller 34. In particular, as previously described, the components of the patient table 20 and the gantry 11 are controlled by way of connections 14, 22 to the control systems 16, 18.
The control systems 16, 18 include a variety of feedback, analysis, and control components that, as will be described, coordinate operation of the system 10 according to one of a variety of operational protocols. In particular, the control systems 16, 18 include a computer and/or backplane 36 that may include a computer, computer network, or other computing system/network. In this regard, it is contemplated that a dedicated operator console 38 may be included that provides a centralized station through which an operator can control a therapy session. The operator console 38 allows the operator to access and control a variety of components, such as a mass storage device 40 having stored therein resources including a priori data tables, or prescribe a therapy session. In the later case, the operator console 38 and backplane 36 coordinate operation of an illumination array power supply 40 and an illumination array controller 42. In accordance with some embodiments, the operation of the array power supply 40 and illumination array controller 42 are controlled by a feedback-dosimetry control system 44 that, in accordance with still other embodiments, coordinates operation of the system 10 using feedback from a detector array data acquisition system 46, spectrophotometric image reconstructor 48, and physiological monitoring system 50.
The physiological monitoring system 50 includes a blood-pressure monitor 52 and/or an exhalation analyzation system 54. Using blood-pressure monitoring 52, the physiological monitoring system 50 and/or feedback-dosimmetry control system 44 and/or the backplane and computers 36 identifies variation in blood-pressure indicative of the desired biochemical state of cytochrome oxidase in the internal target area of the patient that are caused by the proper dose and wavelength of near-IR light transferring the proper amount of energy to the target area. For example, the system seeks to identify a drop in blood pressure indicative of the activation of the heme enzyme, soluble guanylate cyclase. Additionally or alternatively, exhalation analyzation system 54 can be used to identify the presence of nitric oxide in the patient's breath that is indicative of the proper dose and wavelength of near-IR light transferring the proper amount of energy to the target area and causing nitric oxide disassociate with cytochrome c oxidase. As will be described, this feedback can be used to non-invasively identify the dose of near-IR light entering the target area and, furthermore, identify a minimum dose of near-IR light needed to perform the desired therapy on the target area.
It is contemplated that the above-described system 10 and treatment process could be implemented in a variety of configurations that may or may not utilize all of the components described above. For example, the instrumentation for generating the visible and near-infrared light to activate cytochrome c oxidase could be arranged as an open-loop visible/near-IR phototherapy device that determines the proper delivery dose based on a priori tissue estimates of scattering and absorption properties. Alternatively, it is contemplated that the instrumentation for generating the visible and near-infrared light may be arranged as a closed-loop visible/near-IR phototherapy device that determines the proper delivery dose based on real-time in-vivo measurements of transmitted and reflected components of optical signals. Also, it is contemplated that the closed-loop phototherapy device may determine the proper delivery dose based on feedback dosimetry as well as an adjunctive spectrophotometric determination of cytochrome c oxidase oxidation states.
Referring now to
Within this open-loop configuration 60, the photons transmitted or reflected during treatment are not measured. In this regard, the open-loop system 60 is highly cost effective and robust. To control the dose light delivered by the beams 64, 66, the system 60 relies on a priori knowledge of tissue optical properties, as related by tissue absorption and scattering coefficients. Fortunately, given the relatively benign effects of visible (e.g., red) and near-IR radiation, over-treatment of tissue may result in little or no adverse effects at the photon intensity levels utilized (i.e., the therapeutic index of visible/near-IR phototherapy is quite high at the power levels of interest). Accordingly, the predominant concern in the case of the open-loop system 60 is that the incident energy exceeds a minimal level capable of resulting in a therapeutic benefit at a local tissue region of interest.
Proper performance and therapeutic response of the system 60 depends significantly on accurate knowledge of the local optical properties of the human tissue being treated. Table 1 provides example data for absorption and scattering coefficients relevant to phototherapy applied in a neurological application.
The administration of a desired photon energy density at a given location of tissue may be estimated from these values, as a function of wavelength. Assuming a simple one-dimensional approximation, one may estimate the photon intensity as a function of depth using a standard exponential model:
I(z)=Ioe−(α+α
Where α and αs are respectively the absorption and scattering coefficients of the local tissue, z is the depth in the tissue, and Io is the intensity incident upon the tissue. The penetration depth at which I(z) decreases to 1/e of the incident value is a function of wavelength, which ranges from approximately 5 mm at 1064 nm to approximately 1 mm at 488 nm.
Referring again to
Once these setup procedures are complete, a main power delivery system is activated so as to apply power to the illumination array power supply, operator console, main computer/backplane, and all subcomponents of the phototherapy system are active and the operator enters appropriate parameters for illumination 82. As illustrated in
After the settings are applied 82, the modules are activated and the illumination is applied to the patient's anatomy (e.g., cranium and brain) for the given length of time 84. Again, the illumination sources in the illumination/detection modules may be LED sources, superluminescent diodes (SLDs), solid state laser diodes, or other light sources. The detector elements (e.g. photodiodes, phototransistors, photoresistors, etc.) in the illumination/detection modules are used to record transmitted and scattered light. This information is passed to the detector array data acquisition system 46 of
Referring now to
Additionally or alternatively, a patient physiology monitor 98 may be used as a feedback source that is connected to feedback/control lines 96 to provide feedback that can be used to perform active control (e.g., amplitude control, etc.) of the dose (e.g., intensity, duration, wavelength, etc.) delivered by the light sources 61, 62. The patient physiology monitor 98 may monitor one or more aspects of the patent for signs of the effective dose and amount of energy delivered to the internal target area 72. For example, the patient physiology monitor 98 may analyze air exhaled by the patient 70 to identify an increased concentration of nitric oxide in the exhaled air because nitric oxide is a molecule that can be used a signal of intercellular activity or change. To this end, when an increase in nitric oxide is detected, it indicates that at least a minimum number of photons in the beams 64, 66 are reaching the internal target area 72. Additionally, it is contemplated that the patient physiology monitor 98 may include a blood pressure monitor because nitric oxide has a role in the control of blood flow and blood pressure via activation of the heme enzyme, soluble guanylate cyclase. Accordingly, the present invention recognizes that nitric oxide targets the mitochondrial oxygen-consuming heme/copper enzyme, cytochrome c oxidase.
In the closed-loop phototherapy system 90, a priori knowledge of absorption and scattering coefficients is not necessary. Instead, the photosensors 92, 94 and/or the patient physiology monitor 98 are used to measure or determine the transmitted or scattered radiation. With respect to using the photosensors 92, 94 for active control, using Eqn. 1, two measurements of intensity can be made, at z=0 (the entry point of the incident radiation) and z=D (the point at which the radiation leaves the tissue after passing through a distance D), as follows:
I(0)=Io Eqn. 2;
I(D)=Ioe−(α+α
Accordingly, the total optical loss (α+αs) can be estimated as:
(α+αs)=D−1·ln(I(0)/I(D)) Eqn. 4.
This value of total optical loss may, in turn, be used to estimate energy density as a function of tissue depth. Thus, the system can affect real-time dosimetry through modulation of the administering optical sources.
Referring to
Once these setup procedures are complete, a main power delivery system is activated so as to apply power to the illumination array power supply, operator console, main computer/backplane, and all subcomponents of the phototherapy system are active and the operator enters appropriate parameters for dosimetry 108. That is, unlike the open-loop operational procedure described with respect to
After the settings are applied 108, the modules are activated and the illumination is applied to the patient's anatomy (e.g., cranium and brain) 110. To achieve the desired dose, the detector elements (e.g. photodiodes, phototransistors, photoresistors, etc.) in the illumination/detection modules are used to record transmitted and scattered light and/or feedback from the physiological monitoring systems are processed 112 and the illumination intensity delivered to the patient is dynamically controlled 114. As will be described, the feedback 112 and dynamic control of dose 114 based on the feedback may not only be utilized to deliver the desired dose to the internal target area, but may be used to identify a minimum effective dose for an individual patient.
After completion of the therapy session 112-114, the illumination/detection modules are deactivated and the results of the phototherapy are evaluated 116 through an examination procedure and the process concludes 118.
Referring now to
As described with respect to
In simplified terms, the system 119 includes a system for phototherapy administration as well as an imaging modality, in which voxel-by-voxel determination of oxidation states of cytochrome c oxidase are reconstructed using techniques similar to those employed in diffuse optical tomography. In this regard, the system 119 may be considered a photo-tomotherapy system.
The system 119 may be extended to more complex systems comprised of multiple optical absorbers/scatterers, such as cytochrome c oxidase, hemoglobin (in its oxygenated and deoxygenated states) and water, by extending the number of source wavelengths. However, the number of discrete wavelengths chosen depends on a number of considerations. For example, one consideration includes the number of biochemical species to be determined from optical measurements (e.g., oxidized and reduced cytochrome c oxidase, oxy- and deoxyhemoglobin, water). Additionally, the number of excess or redundant data points utilized to improve the accuracy of the measurements, through inverse solution of an over-determined set of data, should also be considered. Furthermore, the particular techniques used to extract individual wavelength data and the limitations of any associated electronics 126, including circuit speed limitations in time-division multiplexing schemes or bandwidth limitations in frequency-division multiplexing schemes, should also be considered. To these ends and others, the overall system complexity and cost constraints will aid the determination of the number of discrete wavelengths utilized by the system 116.
Using multiple wavelengths to perform spectrophotometric measurements in addition to the dosimetry techniques described above adds an additional and powerful tool to the phototherapy system 116. In particular, the system 116 is capable of noninvasive measurement of the underlying biochemical processes. The techniques for this determination rely on an inverse solution of a three-dimensional partial differential diffusion equation describing photon migration through an absorbing/scattering medium, which is given by:
∇·D(r)∇Φ(r,ω)−[μa(r)−iω/c] (r,ω)=−S(r,ω) Eqn. 5;
where Φ is the photon density as a function of frequency (wavelength) and distance into the medium, D is the diffusion coefficient (a function of absorption and scattering coefficients), and S represents the source distribution. Therefore, by applying a known distribution of source radiation and measuring the photon flux as it exits the tissue volume under consideration, it is possible to determine D (i.e., absorption and scattering properties) through an inverse solution of the differential equation above.
While serving as a powerful spectrophotometric technique, this approach is computationally intensive, requiring high-speed computational equipment for real-time implementation. However, a number of solutions have been presented to address efficient approaches to the solution of the above differential equation, as well as questions of the existence and uniqueness of the inverse solutions thereof.
Referring now to
In accordance with one embodiment, the multi-wavelength therapy session 138 includes a time-division-multiplexed delivery method, in which all sources at ‘wavelength 1’ are first applied for a given interval, then all sources at ‘wavelength 2’ for a given interval, then all sources at ‘wavelength 3’ for a given interval, and so on, in a repetitive cycle. Alternatively, the multi-wavelength therapy session 138 may include frequency-division-multiplexed delivery method, in which sources of ‘wavelength 1,’ ‘wavelength 2,’ ‘wavelength 3,’ and so on are encoded with a uniquely-identifying modulation frequency that is significantly lower than the frequency of the unmodulated light signal. Also, it is contemplated that other delivery methods may be utilized, for example, in combined time and frequency modulation.
During the multi-wavelength therapy session 138, dosimetry feedback is received from the physiology monitoring system and the detector elements (e.g. photodiodes, phototransistors, photoresistors, etc.) in the illumination/detection modules. The feedback from the detector elements is used to record transmitted and scattered light for each of the individual source wavelengths. This is accomplished using time-division-multiplexed signal receivers, frequency-division-multiplexed signal receivers, or other schemes to determine transmitted and scattered light for each individual source wavelength. This information is passed to the detector array data acquisition system. In accordance with this configuration and mode of operation, the information recorded by the detector array data acquisition system 46 is used to adjust parameters for the illumination array power supply and illumination array controller in real-time during the therapy session, so as to achieve a desired dose within the internal target tissue 142. The dosimetry feedback in this arrangement and operation may utilize information about scattered/transmitted light at one, two, or more of the source wavelengths. In particular, the spectrophotometric image reconstructor 48 of
After completion of the therapy session 138-142, the illumination/detection modules are deactivated and the results of the phototherapy are evaluated 144 through an examination procedure and the process concludes 146.
Therefore, the above-described systems and methods provide a variety of designs and implementations for the administration of phototherapy, along with “imaging-feedback” techniques for dosimetry and spectrophotometry. While the open-loop system is cost-effective and computationally simple, it depends on accurate a priori knowledge of tissue properties. The closed-loop systems provide accurate dosing. When coupled with spectrophotometric techniques, the systems are capable of direct, non-invasive monitoring of the underlying biochemical processes.
The feedback and control systems described above may not only be used to maintain a proper dose during a therapy session, it is contemplated that the feedback and control systems may be utilized to determine a desired and/or minimum effective dose. Referring now to
Specifically, as described above, feedback is received from the physiological monitoring system 50 of
By providing a very low initial/calibration dose 156, it can be expected that the initial feedback will not indicate a proper dose level 162 and the dose is slightly increased 164. By repeatedly increasing the dose 164 and monitoring the dose feedback 158, the system can determine when the proper/minimum dose is delivered 160, 166. This same process may be used to identify other parameters for a therapy session, such as wavelength, and the like. For example, instead of starting at a minimum dose and incrementally increasing the dose, a base wavelength may be initially used and incrementally adjusted to identify an optimum wavelength. To this end, the feedback systems can be used to non-invasively identify desirable operational parameters of near-IR light entering the target area, such as identifying a minimum dose of near-IR light needed to perform the desired therapy on the target area.
Once the desired operational parameters are selected/determined, the therapy session is performed 168, for example, for a desired duration of approximately 3 minutes. That is, in developing the present invention, it was determined that extended durations of therapy sessions, for example, extending beyond 10 to 30 minutes and, in some cases, extending beyond only 4 to 5 minutes provided no additional benefit beyond that initially gained by the first 3 to 4 minutes. Following the therapy session 168, the patient is evaluated 170 and the process ends 172. However, it is contemplated that the above-described therapy process 148 is part of an overall therapy regiment. That is, the development of the present invention also identified that, while extended therapy sessions showed diminishing returns, multiple individual therapy session at regular intervals is quite beneficial. Therefore, it is contemplated that the above-described processes may be performed multiple times per day, for example twice a day, every day.
The above-described systems are capable of producing near-IR light at a wavelength, for example, 670 nm, to provide a treatment that attenuates cytotoxity and dopaminergic cell death in a patient with Parkinson's disease and significantly improves clinical outcome. The specific wavelength of the near-IR light is selected based on the particular pathology for which the treatment is targeted and may be determined from a priori knowledge or may be determined using the above-described feedback systems. As will be shown below, in the case of Parkinson's Disease, which combines genetic susceptibility and mitochondrial toxicity, a wavelength of approximately 670 nm has been determined to be desirable.
To determine a desirable wavelength, confluent cultures of human dopaminergic cells (SH-SY5Y) engineered to stabily overexpress the A30P mutant form of α-synuclein were exposed to increasing concentrations of the dopaminergic toxin MPP+ (0-5 mM) for 14 hours. Cell proliferation (protein concentration and MTS assay), mitochondrial function (mitochondrial dehydrogenase activity), oxidative stress (H2O2 production), and cell viability (LDH release) were assessed 12 hours later. Experimental cultures were treated with 670 nm LED arrays (GaAlAs LED; bandwidth 670+25 nm at 50% power). An LED array can be created from LEDs that are commercially available, such as from Quantum Devices, Inc., of Barneveld, Wis. Culture plates were placed directly on the diode array unit. Treatment comprised irradiation at 670 nm for 5 minutes resulting in a power intensity of 50 mW/cm2 and an energy density of 8 joules/cm2. The near-IR LED treatment was administered at 1, 15, 26 hours after MPP+ exposure. Exposure to MPP+ produced a concentration-dependent decrease in cell proliferation, mitochondrial function, and cell viability accompanied by a concentration dependent increase in reactive oxygen species production.
Three 670 nm LED (8 J/cm2) treatments significantly attenuated the cytotoxic actions of MPP+ resulting in increased cellular proliferation, profoundly enhanced mitochondrial function, reduced oxidative stress and increased viability.
Additionally, the 670 nm photon irradiation ameliorated the toxicity of the Parkinsonian drug 1-methyl-4-phenyl-1,2,3,6-tetrahydropyridine (MPTP). Mammals treated with MPTP develop the cardinal features of Parkinson's disease, akinesia and loss of dopamine in the basal ganglia, within hours. The rapid onset of the Parkinsonian syndrome following acute MPTP intoxication thus provided an excellent paradigm for the initial assessment of the therapeutic potential of near-IR photon therapy. Administering MPTP to simulate Parkinson's disease has the added advantage that it poisons the very process thought to account for the beneficial actions of near-IR light, namely mitochondrial energy production. To investigate the ability of near infrared light at 670 nm to ameliorate the acute toxicity of the Parkinsonian drug MPTP, C57BL/6 mice (20-25 g) were either pretreated with 670 nm photon irradiation or were treated subsequent to MPTP treatment. The MPTP (saline control) was administered subcutaneously at a dose of 50 mg/kg. Mice were then subjected to behavioral testing.
To administer the near-IR light, a system consistent with the above described system 10, and having LEDs arranged as will be described below was used. Specifically, the LED arrays were arranged to lie on 4 sides of a Perspex 4-mouse animal restrainer, such that the mice were illuminated from the top, bottom and both sides resulting in a power intensity of 25 mW/cm2 per array and a calculated dose of 6 J/cm2 per minute of exposure. For behavioral testing, plexiglass cages with white floors and translucent walls were used as the open field (26×26×39 cm). Behavioral activity was measured using infrared beams. The patterns of beam breaks were computed (Truscan Software) to obtain parameters of locomotor activity. Each animal was tested from 0-12, 23-24, 47-48, and 71-72 hours post injection.
The MPTP was metabolized to MPP+ within 5 minutes and caused a major depression of dopamine in the striatum and substantia nigra within 15 to 30 minutes. These changes suggest the major effects of MPTP are induced within the 15 to 30 minutes of its administration. A single 670 nm LED treatment of 10 minutes with a dose of 60 J/cm2 was administered following MPTP, but did not alter the changes in loco-motor behavior brought about by MPTP. These studies suggested that 670 nm LED treatment was not able to reverse the effects of MPTP when given after the toxin, at least, in the paradigms tested. This finding is consistent with previous studies suggesting that the activation of cell signaling pathways, gene transcription, and protein synthesis are required for the cytoprotective actions of near-IR phototherapy.
Consequently, testing the ability of pretreatments at 670 nm to affect MPTP-injected mice showed that a pretreatment for 5 minutes (30 J/cm2) twice a day over 3 days attenuated the deficits in loco-motor behavior induced by a single injection of MPTP. The LED pretreatment attenuated the effects of MPTP on the length of time spent moving, the number of movements made, the distance moved, and the velocity. Moreover the 670 nm LED pretreatments essentially restored these behaviors to control levels by the end of a 48 hour period. Remarkably, the 670 nm LED pretreatment attenuated MPTP-induced weight loss (12% weight loss vs. 33% weight loss) and prevented the MPTP-induced death of the animals. Taken together, these observations demonstrated a clear therapeutic benefit of 670 nm LED pretreatments against the acute toxicity of MPTP.
Additionally, calculations regarding the feasibility of delivering a therapeutic dose of mid-infrared radiation to the substantia nigra were completed using a Monte Carlo simulation to approximate the diffusion of photons from a surface emitter located on the scalp through multiple layers of tissue. Optical properties at 800 nm were assumed as follows in Table 2:
Instead of a curved/spherical geometry, we assumed a slab with the tabulated optical properties. Superposition of the results from the representative case for any given angle of approach should be valid with the assumption that the layered structure outlined in Table 2 is valid for any direct external path through the scalp to the mid brain. In fact, expansion of the source to include an emission surface equivalent to the surface area of the scalp (like a swimmers cap) is valid as long as the bones of the base of the skull are avoided.
From the measurements provided from imaging, it is evident that the substantia nigra resides approximately 8-9 cm deep from most external approaches; however, the final layer of the model was allowed infinite depth to “catch” all photons. For ease of scaling, a source of even irradiance (flat top) and a circular geometry (1 cm diameter) was assumed. Similarly, a total power of 1 watt was assumed at the surface, resulting in a modeled irradiance of 1.27 W/cm2.
The average value over all the grids from 8-9 cm depth was 1.5×10−5 W/cm3 to 2.5×10−5 W/cm3, giving a local irradiance within the tissue of approximately 1.3×10−4 W/cm2 to 1.8×10−4 W/cm2. So, from the model, to achieve a desired therapeutic dose of 5 mW/cm2 at a depth of 8 cm, a single 1 cm diameter source would need to have an irradiance of approximately 39 times the original 1.27 W/cm2 used in the model or 49.8 W/cm2. The maximum permissible exposure calculated from the ANSI standard lists for skin as 0.32 W/cm2. Therefore, the required source irradiance is 156 times MPE for a 1 cm diameter source.
Based on the approximation derived via this Monte Carlo model, to achieve a therapeutic dose of 5 mW/cm2, the surface area of an 800 nm source at the scalp would need to be ˜160 times larger than the source used in the simulation. Such is achievable with the above-described gantry system or a localized “bonnet” configuration. However, in the bonnet configuration some active cooling may be desirable. Alternatively, it is contemplated that a more direct approach may be used by illuminating through the roof of the nasal cavity/cribriform plate. Such could be accomplished with a source irradiance in the range of 50 mW/cm2, assuming a source size at the nasal mucosa of approximately 0.8 cm2.
The above described systems and methods can also be used in the treatment of other pathologies, such as cancerous tumors, for example, recurrent brain tumors. Photodynamic therapy involves the selective retention of a photosensitizer that upon activation with light mediates tumor cell destruction via the production of singlet oxygen. The cytotoxic photodynamic effect on tumor cells depends on the interaction of localized photosensitizer, light, and oxygen. Experimental and clinical studies indicate selective accumulation of photosensitizing drugs in brain tumors. In clinical practice the most common photosensitizer administered for brain tumor is hematoporphyrin derivative (HPD) and Photofrin porfimer sodium. Both of these photosensitizers are an inhomogeneous mixture of molecules that have two significant absorption peaks at 390 and 630 nm.
Light penetration into brain and tumor tissue increases with longer wavelength light. Thus, because of the infiltrative nature of many brain tumors and in particular malignant gliomas, 630 nm laser light is frequently used as a light energy source. Traditional light delivery systems that target tumor tissue are invasive and rely on fiber optics that are directly inserted into the tumor or with an inflatable balloon adapter that is placed into the resection cavity. The above-described system is capable of delivering the desire light in highly controllable dosages to the desired locations non-invasively.
The above-described systems and methods are capable of treating the entire brain, lung, liver, gastrointestianal tract, arm, leg, spinal cord or the like by providing a full-circumference photon convergence array. While radiation therapists have used surrounding arrays of gamma sources for the treatment of cancer, the present invention provides the ability to deliver near-IR (and also other light ranges) photons to large volumes of tissue to provide the light needed for healing deep inside the body. By evenly placing light source arrays all around the target, it is possible to use the physics of light convergence to our advantage while compensating for the diminishing power over distance of our current light source arrays.
The above-described systems and methods have applicability for treating a wide variety of pathologies. For example, a head injury protocol can be designed that includes the even treatment of the entire brain to minimize the effects of closed head trauma. Additionally, with respect to mucositis study, the above-described system could be used to treat the entire gastrointestianal tract, the entire spinal cord. These treatments for preventing mucositis in bone marrow transplant patients may be much more effective than traditional treatment methods because the above-described systems and methods allow treatment of the entire gastrointestinal tract. In this regard, the future of treating major musculoskeletal regions deep inside muscle and bone in arms and legs will also depend upon deep, even light delivery.
The present invention has been described in terms of the preferred embodiment, and it should be appreciated that many equivalents, alternatives, variations, and modifications, aside from those expressly stated, are possible and within the scope of the invention. Therefore, the invention should not be limited to a particular described embodiment.
This application is based on provisional application 60/820,980 filed Aug. 1, 2006, entitled “SYSTEM AND METHOD FOR CONVERGENT LIGHT THERAPY HAVING CONTROLLABLE DOSIMETRY,” and claims the benefit thereof.
This invention was made with government support under Grant No. 5R21AT003002-02 from the National Center For Complementary and Alternative Medicine of the National Health Institute. The United States Government has certain rights in this invention.
| Number | Date | Country | |
|---|---|---|---|
| 60820980 | Aug 2006 | US |
