Near-infrared photonic energy penetration: can infrared phototherapy effectively reach the human brain?

Introduction

Traumatic brain injury (TBI) and stroke are major sources of morbidity and mortality worldwide. The World Health Organization has projected that TBI soon will be the third most frequent source of disability.¹ Stroke is the second leading cause of death worldwide.² While attention to the pathophysiologic processes that underlie neurotrauma has yielded considerable information, efficacious treatment strategies have yet to emerge. Treatment of neurological trauma is largely limited to mitigating the symptoms (see Morries and colleagues³ for review). Over the past decade, near-infrared light (NIR) has gained attention as a potential treatment strategy for TBI and stroke in both the acute and chronic setting.

NIR has been investigated for its ability to modulate intracellular reparative mechanisms. NIR can facilitate wound healing^4,5 and promote muscle repair⁵ and angiogenesis.^4,5 The application of NIR by low power laser or by light emitting diode (LED), referred to as either laser phototherapy⁶ or near-infrared photobiomodulation,⁵ has been studied and applied clinically in a wide array of ailments, including skin ulcers,⁷ osteoarthritis,⁸ peripheral nerve injury,^4,5 low back pain,⁹ myocardial infarction,¹⁰ and stem-cell induction.¹¹ Since NIR passes relatively efficiently through bone, several studies of transcranial near-infrared light therapy (NILT)¹² in animal models of brain damage have been conducted by multiple laboratories. A large clinical trial of NILT for acute stroke showed clinical improvement – NeuroThera Effectiveness and Safety Trial (NEST)-1;¹³ however, a subsequent Phase III clinical trial failed to show benefit at an interim futility analysis.¹⁴ This and other findings of ineffective protocols for NIR in a variety of pathological conditions^15,16 raise an important question about the necessary elements of an effective therapy.

This review focuses on the relevant mechanisms of brain injury and NIR as it relates to the therapeutic use of NILT. To understand the ability of NILT to repair damaged or dysfunctional brain tissue resulting from stroke and TBI, it is first necessary to understand the relevant pathophysiological mechanisms of brain injury. Then the postulated mechanisms of NIR in mitigating these mechanisms will be reviewed. The physical properties of light and the manner in which it interacts with tissue are then elucidated. The ability of NIR to penetrate to sufficient depth with sufficient energy to exert a biological effect on the brain is key. Data on light penetration are provided and discussed in the context of the current literature on the topic.

Pathophysiological mechanisms of neurotrauma

TBI is a complex injury in which the nature of the sequelae depends on the region of the brain involved, injury severity, patient’s age, and the nature and delay in initial care. TBI disrupts membrane function and gives rise to early ionic and neurotransmitter perturbations.¹⁷ Together with a substantial release of the excitatory neurotransmitter glutamate, these perturbations initiate a cascade of events that extensively disrupts normal cellular function, alters glucose metabolism, induces free radical production, and impairs mitochondrial function.^17–20 An early event is increased release of potassium which is proportional to the severity of the injury.¹⁹ This has a robust inhibitory effect on neuronal activity. Calcium (Ca²⁺) begins to accumulate within neurons and significantly impairs function. Increased intracellular Ca²⁺ activates mitochondrial uptake, leading to Ca²⁺ overload in mitochondria,¹⁷ oxidative stress, and impaired mitochondrial function.^19–21 Accumulations of Ca²⁺ can directly destroy portions of the diverse mitochondrial population²² and induce persistent damage in surviving mitochondria²³ (although, see Pandya et al²⁴). Early excess glutamate can deplete metabolic pathways. Increased reactive oxygen and nitrogen species can indirectly deplete energy precursors and induce peroxidation of mitochondrial (and cellular) lipid membranes.^20,25–27 The byproducts of lipid peroxidation have been implicated in inactivation or disruption of mitochondrial (and cellular) proteins.²⁶ Mitochondrial DNA is particularly vulnerable to oxidative damage. As a result, all 37 mitochondrial DNA genes are disrupted, as well as 235 additional nuclear DNA genes.²⁸

Glucose is the primary energy source for neurons, but becomes considerably less available following TBI. Studies of cerebral glucose metabolism and fluorodeoxyglucose positron emission tomography have shown an initial brief increase in glucose metabolism, likely associated with glutamate flooding.¹⁸ Decreased glucose metabolism follows within 1 hour of injury and appears to be proportional to the severity of the injury.^20,29 During the first 3–4 days, cerebral perfusion can be increased¹⁸ and a spreading depression of neuronal function and metabolism can occur. This is followed by a prolonged depression of both cerebral perfusion and cerebral glucose metabolism which has been shown in both humans^30–32 and animal models.^29,33 In addition, glucose transport from blood vessels is disrupted.³⁰ Moreover, glucose appears to be shunted from mitochondrial pathways to the pentose phosphate pathway.^17–20,29 Overall these changes create an energy crisis inside the affected neurons.

This energy crisis promotes the increased concentration of free radicals, due to increased pentose phosphate metabolism, reduced mitochondrial function, and impaired free radical scavenger mechanisms.¹⁹ The consequences of increased free radicals can be far-reaching including propagation of additional free radicals, breakdown of lipids within membranes,³⁴ edema, inflammation, and DNA damage.^18,35

Neuroinflammation is an additional and incompletely understood mechanism in TBI. Recent evidence has shown that neural inflammation can persist for years following an injury.^36–38 Using a positron emission tomography ligand for inflammation, one group demonstrated patients could have elevated inflammation 11 months to 17 years after a TBI.³⁹ Notably though, areas of accumulated inflammation marker did not correspond to areas damaged directly by TBI. Altogether, these mechanisms appear to contribute to a progression in the size of the initial injury to involve surrounding areas (penumbra).^36–38

In contrast to acute TBI, neurophysiological dysfunction in chronic TBI is less well understood. It is clear that mechanisms activated in acute TBI,¹⁸ such as neuronal injury and apoptosis, would have persistent consequences. Studies have shown that diffuse and Wallerian white matter degeneration occurs following TBI.^40,41 In many ways, stroke and TBI share these long-term mechanisms.^42,43 Long-term disruption of mitochondrial membranes by lipid peroxidation, disrupted Ca²⁺ regulation, loss of subpopulations of mitochondria, and reduced energy production can continue long past the acute phase of TBI.⁴³ In humans, impaired mitochondrial function may persist for months to years based on observations of decreased glucose metabolism in patients using fluorodeoxyglucose positron emission tomography.^31,44 Decreased cerebral blood flow to the injured area also persists for many years based on perfusion single photon emission computed tomography scans.^32,45 Injured and disrupted axons, as well as altered proteolytic pathways in injured neurons, can lead to the accumulation of amyloid precursor proteins and tau proteins.⁴⁶ Accumulations of these abnormal proteins can set in motion a sequence of pathophysiological processes leading to Alzheimer’s disease,^47,48 chronic traumatic encephalopathy,^46,49 and Parkinson’s disease.^48,50,51 Blast injury may be particularly harmful, resulting in persistent axonal abnormalities of varicosities and accumulated abnormal proteins.⁵² Recent evidence has shown a strong correlation between persistent areas of disrupted white matter, shown by diffusion tensor imaging, and areas of decreased cerebral blood flow which were present at the time of injury.⁴¹ In the next section, the mechanisms by which NIR can potentially restore, repair, or mitigate the pathophysiological processes involved in TBI are elaborated.^4,53–55

Mechanisms of photobiomodulation

Primary events

The precise mechanisms underlying photobiomodulation and its therapeutic benefits are not fully understood. The purported effects of NIR are illustrated in Figure 1. Light in the wavelength range of 600–1,200 nm has significant photobiomodulation capability.⁵⁶ Current data most strongly support that absorption of NIR photons by cytochrome c oxidase (COX) in the mitochondrial respiratory chain is the key initiating event in photobiomodulation.^4,54,56 COX is a large transmembrane protein of the inner mitochondrial membrane. It contains two copper (Cu) centers and two heme-iron centers. These metal centers have different light absorption peaks. Reduction of CuA occurs with 620 nm, oxidation of CuA occurs with 825 nm, reduction of CuB occurs with 760 nm, and oxidation of CuB occurs at 680 nm.⁵⁴ These peaks correspond to the “optical window” associated with the biological effects of NIR. Irradiation of COX increases the activity of the entire electron transport chain producing more adenosine triphosphate (ATP). In addition, COX is auto-inducible and its gene expression is activity dependent, such that NIR irradiation may increase the amount of available COX over time.⁵⁷

Figure 1 Hypothesized mechanism of action of near-infrared light (NIR) photobio-modulation. Notes: NIR (600–980 nm) penetrates tissue to variable depth depending on wavelength, coherence, time, and the tissue involved. A portion of the photonic energy reaches the mitochondria and is absorbed by cytochrome c oxidase. In addition to inducing increased adenosine triphosphate (ATP) production, NIR appears to initiate increased production of reactive oxygen species (ROS), reactive nitrogen species (RNS), and possibly (?) nitric oxide (NO). Downstream events include increased early response genes – c-fos, c-jun – and activation of nuclear factor kappa-B (NF-κB), which in turn induces increased transcription of gene products leading to neurogenesis, synaptogenesis, and increased production of growth factors and inflammatory mediators. Abbreviation: ↑, increase.

NIR’s effect has been studied in isolated mitochondria preparations. Irradiation with 632 nm light results in increased proton electrochemical potential and increased ATP production.⁵⁸ COX activity and oxygen consumption also increases.⁵⁹ In a more recent study, Yu et al⁶⁰ confirmed increased oxygen consumption and showed increased activation of several electron transport chain components. In the setting of acute neurotrauma, this increase in energy supply may be sufficient to reduce the consequences of injury. Neurons are often forced into anaerobic metabolism, which results in acidosis, insufficient energy to maintain ion pumps, and calcium overload. Later in the sequence of events following neurotrauma, more energy is required than at baseline due to the large energy requirements of repair. Increasing ATP during acute neurotrauma alone may be sufficient, but NIR appears to initiate a number of other events in the mitochondria.

Secondary events

In addition to the increase in ATP, the change in redox state leads to greater oxidation and activation of the mitochondrial permeability transition pore which alters intermembrane potentials within the mitochondria.⁶¹ This may have a direct or indirect effect on gene transcription and protein synthesis.⁶² For example, transcription factors, such as redox factor-1-dependent activator protein 1, activating transcription factor/cyclic adenosine monophosphate response element binding protein (ATF/CREB), and hypoxia-inducible factor alpha, are upregulated in response to changes in redox states. The change in redox state and NIR possibly directly^63,64 result in the production of reactive oxygen species (ROS), the most common of which is superoxide. Similarly, NIR (670 nm) modulates the effects of reactive nitrogen species in a model of multiple sclerosis.⁶⁵ ROS are potent second messenger molecules. ROS are involved in cell signaling, enzyme activation, nucleic acid synthesis, protein synthesis, and the activation of transcription factors.

The change in oxidation also likely contributes to the displacement of nitric oxide (NO) from the COX molecule. When bound, NO functions as an inhibitor by displacing oxygen from the binding site on COX. When NO is displaced, there is an increase in the activity of the electron transport chain.⁶⁶ In addition, NO serves as a vasodilator and thus increases local blood flow.⁶⁷ NO also functions as a second messenger. Numerous tissue culture and animal studies have demonstrated the effect of NIR on NO levels,^4,68,69 including the upregulation of NO synthase expression.⁷⁰

Nuclear factor kappa-B (NF-κB) is a redox sensitive transcription factor.⁷¹ This pro-survival transcription factor modulates the expression of numerous genes, including ones involved in inflammation, early response (heat shock), anti-apoptosis, cellular migration, and cell survival.^71,72 NIR (810 nm) activates NF-κB apparently via ROS in cultured fibroblasts.⁷² NF-κB can be activated by ROS and indirectly by the effects of ROS on inflammatory cytokines (eg, tumor necrosis factor, interleukin-1).⁷³

Tertiary events

With NIR exposure, induction of mitochondrial RNA synthesis,⁷⁴ as well as protein synthesis, occurs.⁷⁵ More recent work has shown NIR induces the upregulation and downregulation of numerous genes both in the nucleus and in the mitochondria of various cell types. Kushibiki et al⁷⁶ have reviewed the mitochondrial RNA expression changes associated with photobiomodulation. Zhang et al⁷⁷ demonstrated changes in mRNA expression of over 100 genes in cultured fibroblasts exposed to 653 nm NIR. Genes involved in cell proliferation, such as mitogen-activated protein kinase 11 (MAPk11), and cell-cycle progression are increased.⁷⁷ Apoptosis-inhibiting genes are upregulated (eg, Janus kinase binding protein). Meanwhile, apoptosis-promoting genes, such as heat shock 70k Da protein 1A and caspase 6, are downregulated.⁷⁷ Expression of genes for antioxidants and inhibitors of the effects of ROS are increased. Similar work in the retina has shown that genes involved in cell survival, antioxidant production, transcription, and growth factor production are also upregulated in neural retina cells.⁷⁸

Data from tissue culture and animal studies of NIR reveal an increase in growth factor expression^68,72,79,80 and subsequent cell proliferation.^4,12,68,69 Examples of these key growth factors include nerve growth factor, brain-derived neurotrophic factor, transforming growth factor-beta, and vascular endothelial growth factor, which may contribute to late brain remodeling after TBI.^{4,12,54,68,73,79–86} For example, a fivefold increase in nerve growth factor mRNA transcription occurred after irradiation of skeletal muscle cell culture with 633 nm NIR light.⁸⁵

Recent data suggest that transcranial NIR phototherapy can increase the process of neurogenesis in adult mice with stroke or TBI. Increased numbers of neuroprogenitor cells have been demonstrated in both the dentate gyrus of the hippocampus and in the subventricular zone of the lateral ventricle of mouse models.^4,87,88 These cells also demonstrate increased expression of a microtubule protein associated with migrating neuroblasts.⁸⁸ Some studies provide evidence that NIR phototherapy may increase the process of synaptogenesis.^4,88 Together, these processes may aid in the neuroplasticity responsible for neural repair and improved function in cases of chronic TBI.

These cellular changes appear to persist for considerably longer than the interval of light application⁸⁹ (when delivered at appropriate wavelengths and amplitudes).⁴ For example, low level (red and) near-infrared light therapy (LLLT) of a power density of 0.9–36 J/cm² applied in a single treatment at 24 hours post-stroke in animal models yielded a reduction in neurological deficits, as well as histochemical evidence of neuron proliferation and migration.^55,88,90,91 A single application of LLLT in rodent models of TBI had similar benefits.^4,87,92–94 Interestingly, these benefits were not immediately apparent. Rather, a delay of 1–4 weeks was noted, consistent with a progressive regeneration cascade set in motion by the NIR exposure.

Summary

During NIR phototherapy, absorption of red or NIR photons by COX in the mitochondrial respiratory chain causes secondary molecular and cellular events, including activation of second messenger pathways, changes in NO levels, and growth factor production. NILT leads to the reduction of excitotoxicity, the production of neurotrophic factors, the modulation of ROS, the transcription of new gene products with protective or pro-proliferative properties, and the release of numerous growth factors for neurons and other cells.^{4,64,68,73,82–84} NIR appears to initiate a cascade of subcellular events which can yield immediate, delayed, and persistent beneficial changes in the injured neuron or other cell.

Properties of NIR

Light has fundamental physical properties which are relevant to its clinical use. Light is a form of electromagnetic radiation which has properties of both waves and particles. Light is characterized by its wavelength (distance between two peaks), frequency, and amplitude. Light is also characterized by its energy content. This energy is quantified as joules (J). The amount of energy delivered per unit time constitutes the power of light in watts (W = J/second). For medical applications, light is typically reported in terms of wavelength (nm), energy (J), irradiance or power density (W/cm²), and radiant exposure or fluence or dose (J/cm²).^54,95

NIR has a number of biological effects, but it is critical to understand the physical interactions between tissue and light. When light impinges on the surface, a portion (~10%) is reflected.⁹⁶ The energy that does penetrate the surface is refracted or bent toward a line perpendicular to the surface. This results from the particle property of light. These particles are, of course, photons. The photons entering the tissue can be transmitted through the tissue, scattered, or absorbed. Scatter increases the volume of tissue impacted by the light. Photons can change direction without loss of energy. Scattering is particularly likely at interfaces between different tissues. Reflection or refraction also occurs at such interfaces. These effects contribute to shortening the distance to which light will travel or penetrate into the tissue.^96–98

Most tissues have the capacity to absorb light energy. Usually this is mediated by a molecule absorbing a photon. Molecules containing metal ions have a strong capacity for absorbing photonic energy, but DNA and water also can. The absorption of energy can induce a change in the confirmation and/or function of the molecule.

Penetration of NIR through tissues is determined by several factors: wavelength, energy, attenuation coefficient (composed of scatter, refraction, and absorption), area of irradiance, coherence, and pulsing. In general, longer wavelengths (up to 1,000 nm) will penetrate deeper; however, the absorption of water begins to predominate above 1,000 nm.⁹⁶ Increases in power density, in general, will lead to greater penetration. More photons will traverse the tissue. The area of surface irradiation also affects penetration due to scattering effects.

Coherence is a property of light waves in which waves of monochromatic light are aligned such that any point on the wave has the same amplitude and position as the equivalent point in an adjacent wave. Temporal coherence reflects the slight variations in the waveform over time. The more consistent the waveform is, the higher the temporal coherence. Monochromatic light typically has high temporal coherence. Spatial coherence results from the divergence of the light from the point of emission.⁶⁶ Laser has virtually no spatial divergence and creates a long narrow volume of coherent light. LEDs are not monochromatic, but emit light in a relatively narrow band over the peak wavelength. LEDs also have significant spatial divergence and therefore a wide volume of space is radiated; however, within that volume only a very small volume contains coherent light. As Karu⁶⁶ illustrates, the result is that noncoherent LED sources likely only provide coherent light in a thin volume, usually at surfaces. In contrast, laser generates a long narrow volume of coherent light which can penetrate deeper into tissues.

When coherent light enters a tissue, slight distortions in the timing and the shape of the waves occur. As a result, interference can occur between the waves. Polarization, the angle at which a wave is vibrating, also contributes to interference. On a single wave basis, interference results when the amplitude of the wave at a given point is different from that of an adjacent wave and of the population of coherent light waves. At the point of difference, the amplitudes can either cancel each other out {[+x] + [−x]}, be additive {[+x] + [+x]}, or any variation in between {[+x] + [−y]}. The result of these interactions is a field of randomly distributed points of increased and decreased light intensity, referred to as a speckle intensity pattern. Speckling can have a significant impact on the effective penetration depth.⁹⁹ As such, areas of high intensity will penetrate further or will have two to three orders of magnitude greater energy at a given depth.⁹⁹

Pulsing of NIR also increases the depth of penetration and the amount of energy delivered to any given point at the peak of a pulse. Yet, pulsing allows for troughs of energy output such that the overall energy delivered to the tissue can be equivalent or even lower than that delivered by a continuous emission. Pulsing is a property of lasers which cannot be duplicated by LEDs.

Limitations of NILT protocols

Prior clinical applications of NIR photomodulation have utilized LLLT emitters and prolonged courses of daily treatments often extending over months.^100,101 For example, the first published study of NIR therapy for TBI in humans described two cases of chronic mild TBI with significant disability.¹⁰⁰ Each patient had marked neuropsychological improvement after a prolonged series of LLLT treatments using 870 and 633 nm LED arrays over 4–72 months. Yet, some clinical and laboratory studies of LLLT have failed to consistently demonstrate benefit.^{15,16,102,103} For example, Lavery et al¹⁵ demonstrated that LLLT (890 nm LEDs delivering 1.3 J/cm² for 40 minutes daily for 90 days) did not yield significant improvement in nerve conduction velocity in patients with diabetic neuropathy. Similarly, treatment of a rat model of contusive spinal cord injury with LLLT (830 nm at 22.6 J/cm² or 670 nm at 28.4 J/cm²) for 30 minutes per day for 5 days resulted in no significant functional improvement and no reduction in lesion size.¹⁶ The identical treatment regimen was applied to a rat model of TBI with no detectable improvement in motor or sensory function or change in lesion size.¹⁶ In this animal model, Giacci et al calculated 2.6 J/cm² reached the spinal cord with each treatment. This is within the range of reported beneficial doses; yet, it was not effective. Note that several studies have shown that LLLT radiant energy is almost completely absorbed in the first 1 mm of skin.^104,105

A clinical example of this discrepancy has unfolded in the clinical trials for the treatment of stroke utilized in the NEST-1 and NEST-2 trials.^106,107 Lapchak¹² reported that the physical parameters of NILT in these studies may have delivered insufficient energy to cortical tissues to be effective. Therein, 808 nm NIR with energy densities of 0.9 J/cm² was applied to the human scalp at multiple sites for a total of 40 minutes.^106,107 Note that animal models of both stroke and TBI indicate NIR energy densities in the range of 0.9–36 J/cm² yields significant biochemical and behavioral changes.^{3,4,81,87–90,93,94} The concern raised from the NEST studies¹² is that current clinical trials using LLLT to treat TBI may yield negative or inaccurate efficacy data, not because of the incapacity of NIR to invoke a change, but due to a dose error. Doses that are effective when directly applied to a monolayer of cells^75,82 or when penetrating 0.2 mm through the skull of a rodent¹⁰⁸ and the 5 mm through the full thickness of the mouse brain,^{4,81,87,88,92–94,109} may be insufficient to penetrate to 20–30 mm into the human brain.

We have been utilizing relatively high power (10–15 W) lasers at the wavelengths of 810 and 980 nm in clinic to treat TBI with positive results.³ The use of NIR in the treatment of stroke and of TBI are reviewed in a companion paper.³ Skin is the first tissue encountered in the clinical application of NIR phototherapy and represents a barrier to effective penetration due to several factors. Human skin has multiple layers and, therefore, multiple interfaces. Each interface is a surface for scatter. In addition, each layer has different inherent optical properties.^97,110 The epidermis, comprised in part of keratin, collagen, lipids, and melanin, has high absorption in the ultraviolet range, but also absorbs light in the infrared range of 600–1,100 nm.¹¹⁰ The dermis, comprised in part of collagen, elastin, and proteoglycans, is of variable thickness and penetration varies as a result. Scattering is a predominate property of the dermis.¹¹⁰ The dermis is also dense with blood vessels and the hemoglobin-rich blood therein. While hemoglobin has absorption peaks at 450, 550, and 600 nm,⁹⁷ it also absorbs photonic energy in the clinical NIR range of 800–1,100 nm.^110,111 The NIR absorption of hemoglobin depends upon its oxygenation status, with carboxyhemoglobin having greater NIR absorption.¹¹¹ Altogether, NIR photonic energy must first overcome the hurdle of penetrating the skin to have an impact on deeper structures.

We have shown clinical improvement in patients with TBI utilizing high power NIR sources, but does high power NIR penetrate deeper and/or with greater fluence compared to LLLT? We have explored NIR penetration of tissues of clinical relevance or previously modeled to quantify the effective penetration at power densities ranging from the 50–200 mW levels used in LLLT^{87,88,90–94} to high power levels used in clinical studies of TBI treatment.³ Specifically, NIR in the wavelengths often used in clinical studies of red and NIR photobiomodulation were utilized (650–670;^16,100 810;^87,93,94 880;¹⁰⁰ 980 nm^112,113). Power levels ranged from 50 to 200 mW to model LLLT and from 6 to 15 W to model high power NIR phototherapy. Specific tissues included sheep skin and human skin to model skin penetration based on issues raised in studies by Kolari and Airaksinen,¹¹⁴ Bjordal et al,⁸ and Esnouf et al.¹⁰⁴ Sheep head, with skin, skull, and brain intact, served as a model of human brain penetration.³

Recent findings concerning NIR attenuation

Ethical considerations

Animal tissue was obtained from local slaughter facilities and no animals were sacrificed exclusively for these experiments. Human tissue was obtained from ScienceCare (Denver, CO, USA), a commercial agency which adheres to all federal and state legal requirements through the Uniform Anatomical Gift Act, and is accredited by the American Association of Tissue Banks. All guidelines for the ethical handling and disposal of human tissue were adhered to strictly. Ethics approval was not sought for the in vivo human tissue studies, because the authors themselves served as the subjects of the tissue experiments. Verbal informed consent was exchanged between the authors in the planning and preparation of these in vivo human tissue studies.

Ex vivo tissue studies

Sheep skin

Lamb heads were obtained within 12 hours of slaughter. Areas of skin were shaved and sections approximately 3×3 cm were excised. The thickness of the skin was measured with precision calipers. A recently calibrated light meter (Ophir-Spiricon LLC, North Logan, UT, USA) was positioned in a custom-made holder with a calibrated carriage to hold an NIR emitter at a fixed and measurable distance from the surface of the light meter. Several different NIR emitters were utilized in this phase of the study to explore the effects of frequency, power density, pulsing, and LED versus laser on the penetration of NIR. Each emitter was positioned in the carriage of the meter holder and set a fixed distance from the meter surface. The baseline light transmission through air at that distance was determined by five separate measurements. The skin sample was then interposed and NIR transmission through the skin sample was measured over five separate trials each lasting 10 seconds. Temperature readings were obtained using a laser digital sensor (Cen-Tec, Kunshan City, People’s Republic of China) from the surface facing the NIR emitter and the surface facing the light meter after each transmission trial. This procedure was repeated for all NIR emitters studied.

A 50 mW LED emitter at 810±20 nm was constructed to emulate commercially available NIR diode devices which are arranged in arrays and utilized in other studies of LLLT for the treatment of the human brain. This LED was constructed by arranging commercially available diodes in a concave metal faceplate to emit 50.4±5.0 mW. This custom device is referred to herein as “Custom LED”. Five commercially available NIR emitters were also evaluated. The In Light pad (In Light Wellness System, Albuquerque, NM, USA) has an array of LEDs emitting 650 and 880 nm light at 200 mW. The Eltech K-Laser 6D is a 6 W emitter (Eltech Srl, Treviso, Italy) with dual wavelengths of 670/970 nm. The LiteCure LT1000 (LiteCure LLC, Newark, DE, USA) is a 10 W adjustable laser NIR emitter with a dual wavelength of 810/980 nm and can be set to continuous or pulsed light emission. The Diowave 810 nm laser (Technological Medical Advancements, Inc, West Palm Beach, FL, USA) is adjustable up to 15 W, has a wavelength of 810 nm, and can deliver continuous or pulsed NIR. The Diowave 980 nm laser (Technological Medical Advancements, Inc) also is adjustable up to 15 W and can deliver continuous or pulsed NIR.

Penetration of sheep skin

Ex vivo studies of NIR penetration through fresh lamb skin revealed a marked decrease in power density through a skin thickness of only 2 mm (Table 1). The Custom 50 mW 810 nm LED did not appear to penetrate 2 mm of skin. Similarly, the commercial 0.2 W 650/800 nm LED system (In Light) did not show any detectable energy penetrating the 2 mm of sheep skin. When compared to the power density of penetration through 2 mm of air, the 6 W LED of wavelength 670/970 nm had an approximately 12%–20% penetration, predominately in the red light range of 670 nm. The 10 W combined 810/980 nm infrared laser (LiteCure) showed a power density drop of 91% across 2 mm of skin. The 15 W 810 nm laser (Diowave) demonstrated a 67% drop in power density, while the 15 W 980 nm laser (Diowave) demonstrated an 86% drop in power density across the same thickness of skin. All of these levels of penetration were statistically significant compared to the LED systems.

Table 1 Data on infrared light penetration of ex vivo skin samples Notes: The manufacturer’s specified watt output, the actual output registered when the infrared light-emitting device was directly in contact with the meter detector, and the watts which traversed 5 mm of air are reported. The watts recorded after infrared light from the device penetrated the stated thickness of skin along with temperature (temp) change at the surface of the skin closest to the infrared emitter also are provided. Data on the effects of pulsing at 10 Hz are provided where relevant. Numbers in bold are percentage change in photonic energy with penetration of interposed tissue versus an equal distance of air. Significance is indicated with superscripted letters – significance level at P<0.0001 as determined by one-tailed t-test with corrections for multiple comparisons. aCustom versus other; bIn Light versus other; cK-Laser versus other; dLiteCure versus other; eDiowave 810 nm versus other; fDiowave 980 nm versus other (P<0.01). Abbreviations: NA, not applicable; LED, light-emitting diode.

Using pulsed infrared light yielded much greater penetration. For example, 13.8% of the power density of a combined 810/980 nm infrared laser with a pulse frequency of 10 Hz penetrated 2 mm of skin compared to only 8.6% of the continuous wave light of similar parameters. The 15 W 810 nm laser with a pulse frequency of 10 Hz had a power density drop of 66% across 2 mm of skin. The 15 W 980 nm infrared laser with a pulse frequency of 10 Hz had only a 39% drop in power density across a similar skin thickness. This difference was not statistically significant with multiple comparisons, but a trend was evident.

One concern about higher-powered infrared light sources is the risk of tissue heating. Here, we observed the low power LEDs made no significant temperature change in the skin samples. The 10 W combined 810/980 nm and the 15 W 810 nm infrared lasers made no significant temperature change when keeping the emitter head in motion. Temperature increase with the 15 W 980 nm infrared laser was 1.33°C. Notably, temperature change using 10 Hz pulsing was not significant.

Animal skin serves as a useful model for human skin but differs from human skin in many ways. The density of hair follicles and melanin in the epidermis represent important differences which could be predicted to impact NIR penetration. We also studied NIR penetration in human skin samples obtained from a tissue bank.

Ex vivo human skin studies

The same protocol was used to measure light transmission through human skin. A full-thickness section of human skin measuring 15×15 cm square was prepared by removing all subcutaneous fat by dissection and isolating separate segments measuring 7×7 cm. The thickness of the human skin was measured with digital calipers. Different NIR emitters were again utilized. Each emitter was positioned in the carriage of the meter holder and set a fixed distance from the meter surface. The baseline light transmission through air at that distance was determined by five separate measurements. The skin sample was then interposed and light transmission through the skin sample was measured over five separate trials each lasting 10 seconds. As shown in Figure 2, LEDs were positioned against the skin sample with an intervening sheet of clear plastic wrap. Temperature readings were obtained using the laser digital sensor from the surface facing the NIR emitter after each transmission trial. This procedure was repeated for all NIR emitters studied.

Figure 2 Ex vivo human skin studies illustrated. Notes: (A) The pad of LEDs is held 2 mm from the surface of the light meter detector. The arrow indicates a row of near-infrared light (NIR) LEDs with a wavelength of 880 nm. The meter reads 0.01 W. (B) Human skin 1.9 mm thick is interposed between the NIR LED and the light meter detector. Thin plastic wrap covers the detector. (C) The NIR LED is covered with thin plastic wrap and placed directly against the sample of human skin. Photonic energy could not be detected passing through 1.9 mm of human skin.

Penetration of human skin

Ex vivo human skin was utilized to study transmission of NIR photonic energy (Table 2, Figure 2). The Custom 0.05 W 810 nm LED did not appear to penetrate 1.9 mm of human skin. The commercial 0.2 W 650/880 nm In Light LED system delivered 0.01±0.002 W across 2 mm of air. No energy could be detected penetrating the 1.9 mm thickness of human skin with this device. Energy from the 10 W combined 810/980 nm infrared laser could be detected penetrating 1.9 mm of human skin and a power density drop of 89% across 1.9 mm of human skin was noted with 0.994 W penetrating the tissue. The 15 W 810 nm laser demonstrated an 83% drop in power density across a similar thickness of human skin with 2.008 W penetrating the tissue. The 15 W 980 nm laser was not tested on human skin. Photonic energy penetration of the two laser devices was statistically different from that of any LED device (which showed no photonic energy transmission through human skin). Penetration of human skin also was statistically different between the two laser devices (P<0.000005).

Table 2 Data on infrared light penetration of ex vivo human skin samples Notes: The manufacturer’s specified watt output, the actual output registered when the infrared light-emitting device was directly in contact with the meter detector, and the watts which traversed 2 mm of air are reported. The watts recorded after infrared light from the device penetrated the stated thickness of skin along with temperature (temp) change at the surface of the skin closest to the infrared emitter also are provided. Data on the effects of pulsing at 10 Hz are provided where relevant. Numbers in bold are percentage change in photonic energy with penetration of interposed tissue versus an equal distance of air. Significance is indicated with superscripted letters – significance level at P<0.0001 as determined by one-tailed t-test with corrections for multiple comparisons. aCustom versus other; bIn Light versus other; cLiteCure versus other; dDiowave 810 nm versus other (P<0.01). Abbreviations: NA, not applicable; LED, light-emitting diode.

For NIR to penetrate to the brain and impact neurological injury (stroke or TBI) or disease, it must be able to reach the depths of the brain with sufficient fluence to trigger molecular events.³ It is not sufficient to reach the cortical surface, as neurological disease involves areas beyond the cortical surface. Indeed, NIR photonic energy may need to reach depths of 3–7 cm. For example, TBI most frequently involves the ventral surface of the frontal lobe, and the anterior and medial temporal lobes.³² Parkinson’s disease involves the substantia nigra and the striatum, both located 4–7 cm from the surface of the scalp. Stroke can often involve the cortical surface, but also impact deeper structures of the brain. In fact, this issue of penetration may have been at the root of the failure of NEST-3^13,106,115 concerning the clinical efficacy of NIR phototherapy for stroke. In that trial, the inclusion criteria concerning stroke locations were broadened to include strokes with deeper areas of involvement.³

Skull and brain

Lamb heads were obtained within 12 hours of slaughter. Lamb heads were bisected with a coronal cut (ear to ear) and the portion of parietal and occipital skull and skin with underlying brain were utilized for NIR transmission studies. The same protocol was used to measure light transmission through the skull, overlying tissue, underlying tissue, and brain tissue of lamb heads. The distance of the linear trajectory though the partial lamb head was measured with digital calipers. The carriage of the meter holder was adjusted to allow sufficient clearance to interpose the large piece of tissue between the NIR emitter and the meter. The baseline light transmission through air at that distance was determined by five separate measurements. As shown in Figure 3, the head sample was then interposed with the skull facing the NIR emitter and the exposed cut surface of brain in contact with the light meter. Light transmission through the sample was measured over five separate trials each lasting 10 seconds. Temperature readings were obtained with a laser digital sensor from the skin surface facing the NIR emitter and the brain surface facing the light meter after each transmission trial. This procedure was repeated for all NIR emitters studied, including the Custom 0.05 W LED device and five commercially available NIR emitters (the In Light 650 and 880 nm emitter, the Eltech K-Laser 6D 6W 670/980 nm emitter, the LiteCure LT1000 10 W adjustable laser NIR emitter with a dual wavelength of 810/980 nm, the Diowave laser adjustable up to 15 W with a wavelength of 810 nm, and the Diowave 980 nm laser adjustable up to 15 W).

Figure 3 Ex vivo brain tissue studies illustrated. Notes: (A) The photonic energy penetrating a fixed distance (3 cm) of air was determined. (B) A section of ex vivo lamb head was prepared which included skull, tissue, and brain. (C) The section was interposed in the space between the infrared light emitter and the light meter detector, both of which were fixed in place. The amount of infrared light energy penetrating the fixed distance (3 cm) through tissue was determined. (D) The temperature change was determined using a digital thermometer before and immediately after infrared light exposure.

Penetration 3 cm into brain

Ex vivo studies of NIR penetration through 3 cm of lamb skull, tissue, and brain in a segmented head revealed a profound decrease in power density which was related to wavelength and wattage (Table 3, Figure 3). The Custom 0.05 W LED did not penetrate 3 cm through either air or brain tissue. No detectible energy from the 0.2 W 650/880 (In Light) LED system could be detected at 3 cm through air or tissue. The 6 W LED (Eltech K-Laser 6D) showed a 99.995% drop in power density across 3 cm of tissue. When compared to the power density of penetration through 3 cm of air, the 10 W 810/980 nm (LiteCure) device showed a 99.65% drop in power density across 3 cm of skin, skull, and brain tissue. The 15 W 810 nm (Diowave) device in continuous (non-pulsed) NIR delivered 2.9% of the surface power density, while only 1.22% of the surface power density at 980 nm reached the 3 cm depth through brain tissue indicating that wavelength is indeed an important parameter in reaching deep tissues. Photonic energy penetration with the laser devices was statistically different from the LED devices; however at this depth, the laser devices did not differ significantly from each other using continuous NIR delivery. Using pulsed NIR emission settings, lower total fluency and heat is delivered to the skin surface, while energy delivered to deeper structures at a pulse peak is greater. Pulsed energy penetration to 3 cm was significantly different between the three laser devices (P<0.01).

Table 3 Data on infrared light penetration of ex vivo lamb skull, tissue, and brain Notes: The manufacturer’s specified watt output, the actual output registered when the infrared light-emitting device was directly in contact with the meter detector, and the watts which traversed 30 mm of air are reported. The watts recorded after infrared light from the device penetrated 30 mm of skull, tissue, and brain, as well as temperature (temp) change at the exterior of the skull (skin surface) and at the interior surface of the brain are provided. Data on the effects of pulsing the infrared light at 10 Hz also are provided where relevant. Numbers in bold are percentage change in photonic energy with penetration of interposed tissue versus an equal distance of air. Significance is indicated with superscripted letters – significance level at P<0.0001 as determined by one-tailed t-test with corrections for multiple comparisons. aCustom versus other; bIn Light versus other; cK-Laser versus other; dLiteCure versus other; eDiowave 810 versus other; fDiowave 980 versus other (P<0.01). Abbreviations: NA, not applicable; LED, light-emitting diode.

Temperature changes at the skull surface ranged from 0.2°C to 3°C. Temperature change in the brain was less than 1°C except when using the 980 nm 15 W laser in continuous emission setting. In the latter case, the temperature variation was quite large. These data show less temperature change using the pulsed setting regardless of wavelength and power.

NIR transmission through living tissue is likely different than through postmortem tissue for a number of reasons. First, cross-linking of proteins is an early and progressive event in death. Second, changes in interstitial fluids occur within hours of death. Third, the perfusion of dermis and deeper tissues in vivo creates scatter and refraction of NIR. Fourth, the flow of blood also disperses heat from the site of NIR application. Lastly, some authors have suggested that NO created at the site of irradiation and carried throughout the body in the blood is responsible for the beneficial effects of NIR phototherapy.¹¹⁶ This effect could account for the clinical benefits seen in TBI if NIR does not penetrate to the depths of 3 cm or greater in living tissue. Jagdeo et al modeled NIR penetration in living human tissue by serving as their own author/volunteers.¹¹⁷ We have replicated some of their work using a higher-powered NIR source. Tissues included hand, cheek, ear, and triceps to model the complex mixture of skin, bone, connective tissues, and other tissues found in the pathway of NIR en route to the brain.

In vivo human tissue studies

The in vivo penetration of NIR through human tissue was measured compared to NIR penetration of air. The Diowave 810 nm high power laser was the only NIR emitter utilized in this portion of the study. The power output was set at 13.5 W for a duration of 5 seconds. First, the thickness of two different human hands was measured with digital calipers. The passage of NIR through 25 or 30 mm of air was repeatedly measured (Table 3). Then, the passage of NIR across the equivalent distance of the palm of a human hand was repeatedly measured. Intervening anatomical structures included skin, tendon, bone, muscle, blood, and connective tissue. In a similar fashion, the thickness of subcutaneous tissue at the level of the triceps muscle was measured with digital calipers. The penetration of NIR through skin, blood, and muscle was compared to NIR penetration through the equivalent distance (20 mm) of air. Measurements were collected on three separate trials.

The penetration of NIR through the 9 mm thickness of human cheek was determined by enclosing the laser light emitter in cellophane and inserting the light emitter into the mouth against the internal surface of the cheek and the sensor was positioned against the external surface of the cheek. The emitter was set at 13.5 W and activated for 5 seconds with a pulse setting of 10 Hz. The protocol was repeated three times. Human structures which were thinner than 9 mm were also measured in an identical fashion, including the web of the human hand (7 mm) and the human ear (5 mm). The latter structure allowed measurement of NIR penetration through anatomical structures of skin, cartilage, connective tissue, and blood. These measurements were replicated three times.

Penetration in human tissue

In vivo human tissue studies were conducted to assess the impact of blood flow and the absence of postmortem protein cross-linking and other possible changes to the manner in which NIR penetrated tissue. Several different tissues were examined (Table 4). Only the 810 nm laser at an output setting of 13.5 W was utilized in this portion of the study. All reported values were statistically different from transmission through an equal distance of air. Pulsed NIR appeared to have greater penetration in living tissue, unlike the finding in postmortem tissue. Only 0.6% of continuous wave NIR energy passed through 2.5–3.0 cm of human hand, while 0.8% of pulsed NIR penetrated the same distance. Penetration also appeared to be greater in living tissues that contained bone (human hand) compared to a similar thickness of subcutaneous flesh. Over 0.8% of the NIR energy passed through 25 mm of human hand, while only 0.3% of NIR penetrated a similar depth of tissue with no bones (subcutaneous flesh). Also, cartilage (ear) appeared to allow greater energy transmission compared to a similar thickness of skin (hand web). Temperature change after 5 seconds was 2°C or less at the skin surface and dropped quickly possibly related to blood flow.

Table 4 Data on infrared light penetration of in vivo human tissue Notes: For each human tissue, the distance measured, the Watts traversing the distance of air, the penetrating that distance in human tissue, and the temperature (temp) change at the skin surface immediately after infrared light exposure are provided. Data on the effects of pulsing the infrared light at 10 Hz also are provided where relevant. Numbers in bold are percentage change in photonic energy with penetration of interposed tissue versus an equal distance of air. aSignificance level at P<0.0001 as determined by one-tailed t-test with corrections for multiple comparisons. Abbreviations: NA, not applicable; LED, light-emitting diode.

Attenuation of NIR energy

Given the much greater distance involved in delivering NIR in effective doses to the human brain, we examined NIR penetration to 3 cm depth through the skin, skull, and brain of ex vivo sheep head. As could be anticipated from the penetration studies of skin, the low power NIR emitters showed no evidence of penetration to this depth. The 6 W NIR emitter transmitted less than 1/10 of 1% of its surface energy through 3 cm of skull and brain. It did demonstrate that red light (670 nm) transmitted better – 22% of the red light energy that traversed 3 cm of air was able to penetrate 3 cm of tissue. High-powered NIR lasers delivered between 0.5% and 3.0% of their energy to the depth of the brain. Notably, penetration to this depth was significantly better using 810 nm NIR than it was when using 980 nm NIR. This is advantageous given the stronger evidence of 810 nm light being effective in photomodulation of neurological function.^{87,88,91–94}

These tissue studies indicate NIR energy penetrates to depths of 3 cm whether in ex vivo or living tissue; however, sufficient energy must be delivered to the skin surface. The 0.2 and 0.5 W NIR diodes yielded no detectable energy at 3 cm depth. High-powered NIR lasers were able to deliver between 0.5% and 3.0% of their energy to the depth of 3 cm in living or postmortem tissue, with living tissue absorbing more energy over the intervening distance. Based on the power density of 55–81 J/cm² delivered to the skin of patients in our clinical cases^3,118 (using a 10–15 W NIR, 810/980 nm, or 810 nm laser), then the expected power density in the human brain at 3 cm depth would be in the range of 0.8–2.4 J/cm² – precisely in the range shown to induce neurological benefit in animal models.^{4,81,87,88,92–94} The safety of NIR exposure at high doses has been explored in animal models^119–121 and in humans.^3,55,115

Putting penetration in perspective

One of the earliest studies of NIR penetration and human skin examined transmittance of 633 nm light through progressively thicker sections of human skin.¹⁰² Penetration through 0.4 mm of epidermis was 78% for 633 nm light and at 2 mm, the energy had dropped to approximately 5% of the incident 633 nm light. Later, the same group found no penetration of infrared light beyond 3 mm using the same light sources.¹¹⁴ Bjordal et al⁸ also concluded that 90% of the energy from 632 nm laser is lost in the skin. NIR at 820 nm has slightly greater skin penetration. Approximately 89% of 820 nm light will penetrate 0.4 mm of epidermis and about 13.5% traverses 2 mm of skin,¹⁰² but 0% reaches a depth of 3 mm.¹¹⁴ Others found 80% of the energy from an 820 nm source is lost in the skin.⁸ Human skin also was examined by Esnouf et al¹⁰⁴ using an 850 nm continuous light source at 100 mW. They reported 34% of the light from the source could penetrate 0.784 mm.¹⁰⁴ The 904 nm laser may have greater skin penetration.⁸ Using rat skin of an unspecified thickness, Joensen et al¹¹³ found 20% of the 810 nm light from a 200 mW source penetrated skin. Our results show considerably less penetration by low level NIR. We found energy from a 50 mW 810 nm LED did not penetrate 2 mm of human or sheep skin. No energy could be detected penetrating either human skin or sheep skin from a commercially available 0.2 W LED (650+880 nm). In contrast, 9% of the energy from the 10 W combined 810/980 nm continuous wave infrared laser passed through 2 mm of skin (human or sheep). The 15 W 810 laser in continuous mode delivered 33% of its energy through 2 mm of skin. While longer wavelength is typically associated with greater penetration, we found that only 14% of the energy from a 15 W 980 nm laser in continuous mode penetrated 2 mm of (sheep) skin. These data are consistent with the transmission properties reported for skin, which has relatively good transmission in the range of 810 nm and somewhat less transmission at 980 nm.¹²² Using pulsed infrared light yielded much greater penetration. For example, 41% of the power density of a combined 810/980 nm infrared laser with a pulse frequency of 10 Hz penetrated 1.9 mm of human skin compared to only 11% of the continuous wave light of similar parameters. The 15 W 810 nm laser with a pulse frequency of 10 Hz showed 69% of the energy penetrated 1.9 mm of human skin compared to only 17% of the continuous wave light of similar parameters.

Thicker segments of tissue have been studied by several groups. Penetration through mouse skull (0.2 mm)¹⁰⁸ and overlying skin with 800–810 nm light from an LLLT emitter ranges from 6.3%⁹⁵ to 46%.¹⁰⁹ Penetration through the entire depth of a mouse brain (3–5 mm) is reportedly 1%–4%.¹⁰⁹ Byrnes et al¹²² examined penetration of 810 nm continuous light from a 150 mW source through skin, muscle, bone, and spinal cord of the rat (~24 mm). They found 6% of the energy penetrated these tissues. Similarly, Giacci et al¹⁶ measured photonic energy transmission through an unspecified thickness of skin and muscle overlying the spinal column of the rat and found 6.6% of 670 nm light from a 0.5 W emitter penetrated this distance. Penetration of 830 nm light was slightly greater at 11.3%.¹⁶ Penetration of these same wavelengths from the skin of the rat head to the optic nerve was estimated at 0.1%.¹⁶ Hudson et al¹¹² precisely measured photonic energy at varying depths of bovine muscle using a 1 W 808/980 nm emitter. They found 808 nm light had greater penetration, despite the premise that longer wavelengths travel further. Indeed, the attenuation of 808 nm light at 3 cm was 99%, quite similar to the findings we describe here in both living human hand and the more heterogenous media of the ovine head.

In living human hand (25 mm), Jagdeo et al¹¹⁷ found only 0.01%–0.09% of 830 nm light from a 0.5 W emitter penetrated this distance. We found that 0.6% of 810 nm light from a higher-powered source (10 W) was able to penetrate 25 mm of skin, bone, and soft tissue. This represents at least a sixfold increase in penetration compared to previous work with low power emitters.

Fitzgerald et al¹¹¹ modeled light penetration into the brain for a 670 nm and a 1,064 nm LED light source emitting 28 mW/cm². Using a diffusion simulation computer model with assumptions of 10 mm of overlying scalp and skull, they derived that 2.5 mW/cm² for 670 nm light and 13 mW/cm² for 1,064 nm light would reach the surface of the cerebral cortex.¹¹¹ They further derived that at the center of the brain (10 mm skull +46 mm brain =56 mm), power density would be approximately 1.2×10⁻¹¹ W/cm² for 670 nm light and 1.4×10⁻⁷ W/cm² for 1,064 nm light.¹¹¹

Jagdeo et al also examined LLLT penetration through isolated human skull from cadaver and found it was limited with only 7.4% of the light from an 830 nm 0.5 W continuous LED device (Omnilux) penetrating the bone.¹¹⁷ Moreover, they found that no more than 0.5% of NIR at 830 nm penetrated approximately 10 mm of frontal skull and overlying tissue in a cadaver model. Also, no detectable NIR penetrated the temporal bone and overlying tissue.¹¹⁷ These studies of LLLT and the computer model indicate that photonic energy from LLLT emitters does not appear to deliver significant fluence to the depths required to treat the human brain.

Our studies of 3 cm of sheep skull, brain, and overlying soft tissue are the closest model of the clinical practice of NILT for TBI. Again, NIR from devices generating less than 1 W could not be detected at this depth. The energy from a 6 W LED system showed a 99.995% drop across 3 cm of tissue. In contrast, 0.14% of the energy from a 10 W 810/980 nm device penetrated 3 cm of tissue. At 15 W, an 810 nm emitter in continuous mode delivered 1.26% of the surface power density and 0.80% of the 980 nm device emissions reached the 3 cm depth through brain tissue. Using pulsed NIR emission settings, a lower overall power density was delivered to the surface; however, similar penetration was achieved.

Some have suggested that NIR has a dosing window and have reported a bimodal response curve, such that high-dose NIR could be detrimental;^4,5 however, others have shown a dose-dependent response to NIR with no detrimental effects at higher doses.⁸⁰

The penetration data mentioned and the data presented herein challenge the presumption that only LLLT protocols spanning weeks or months would possibly be clinically effective. For example, using a 0.5 W 830 nm LED, Jagdeo et al¹¹⁷ estimated the power density reaching the cerebral cortex based on their model was 3 mW/cm², which equates to a fluence of 0.0064 J/cm² – 1/140th of the minimum thought to be necessary for ideal photobiomodulation.⁵ Anders and colleagues noted NIR penetrates 4 cm into human cadaver skin, skull, and brain using a 5 W laser (JJ Anders, personal communication, January 13, 2015). From our data, we estimate that in our clinical applications of high-powered NIR lasers,³ we are delivering 0.64–1.95 J/cm² to a depth of 30 mm. This is 100-fold greater fluence than that delivered by an LED system, but within the range of fluence shown to have beneficial biological effects.

Conclusion

Extensive research has shown the fluence within the range of 0.9–15.0 J/cm² is most effective in activating the biological processes involved in reversing or mitigating the pathophysiological effects of TBI. The attenuation of NIR energy as it passes through tissue has been examined in computer simulations, animal tissue, and human tissue. NIR penetration in the human brain is subject to attenuation by multiple tissues (skin, skull, dura, blood, cerebrospinal fluid) and multiple interfaces which scatter, absorb, and reflect the NIR to varying degrees. We have shown through the use of higher wattage NIR lasers that we can deliver fluence at therapeutic levels to the depths of the brain without tissue heating or damage. The protocols have been applied in our clinic with excellent clinical results and no side effects.

Acknowledgments

The authors would like to acknowledge the technical assistance of Phillip Hardinger, DC, DABCO, and Mr Charles Vorwaller (Diowave Corporation/LiteCure Corporation). Artistic creation Figure 1: Ms Taylor Tuteur.

Disclosure

Dr Larry Morries is CEO of the Neuro-Laser Foundation, a nonprofit foundation. He has a private practice in Lakewood, CO, USA.

Theodore A Henderson is president of The Synaptic Space, a medical consulting firm and president of Dr Theodore Henderson, Inc, a clinical service firm. He is also co-owner of Neuro-Luminance, a clinical service organization, president of the International Society of Applied Neuroimaging, and CFO of the Neuro-Laser Foundation.

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