Abstract

Background:The development in the last decade of noninvasive, near infrared spectroscopy (NIRS) analysis of tissue hemoglobin saturation in vivo has provided a new and dramatic tool for the management of hemodynamics, allowing early detection and correction of imbalances in oxygen delivery to the brain and vital organs.

Description:The theory and validation of NIRS and its clinical use are reviewed. Studies are cited documenting tissue penetration and response to various physiologic and pharmacologic mechanisms resulting in changes in oxygen delivery and blood flow to the organs and brain as reflected in the regional hemoglobin oxygen saturation (rSO₂). The accuracy of rSO₂ readings and the clinical use of NIRS in cardiac surgery and intensive care in adults, children and infants are discussed.

Conclusions:Clinical studies have demonstrated that NIRS can improve outcome and enhance patient management, avoiding postoperative morbidities and potentially preventing catastrophic outcomes.

Keywords: INVOS, near infrared spectroscopy, noninvasive monitoring, Hemodynamic management, CO2 reactivity, tissue oxygenation

NEAR INFRARED SPECTROSCOPY

Noninvasive, transcutaneous oximetry based on near infrared (NIR), diffuse reflectance spectroscopy has rapidly become a standard of care. While pulse oximetry is used to indicate arterial hemoglobin saturation, venous oximetry is used to measure tissue hemoglobin saturation in the capillary beds, reflecting O₂ delivery and demand in the tissues. This simple, noninvasive technology is based on complex and in-depth chemical principles that have been refined over the last 80 years to provide unique and invaluable insights into oxygen biology.

The use of NIR light of 700–1000 nm wavelength for spectroscopic analysis of hemoglobin saturation in vivo is based on the fact that very few substances in tissue absorb NIR light, allowing for deeper light penetration. The absorption of electromagnetic radiation from X-ray to infrared wavelengths by chemical compounds is specific to the structure of the molecule being analyzed, with specific molecular bonds absorbing specific wavelengths of radiation. Accurate analysis of a compound normally requires that it be in a highly pure state without any contaminants, unless the contaminants do not absorb the specific wavelengths of radiation.

Metalloproteins with prophyrin rings are the only biologic structures that absorb much NIR light and the hemoglobin molar absorptivity at these overtone (harmonic) wavelengths is extremely low. The cytochrome enzymes absorb NIR light but the tissue concentration is an order of magnitude lower than hemoglobin. Additionally, myoglobin desaturation is limited, allowing the analysis of saturation to be hemoglobin specific.[ 49 ]

NEAR INFRARED SPECTROSCOPY AND TISSUE OXYGENATION

Millikan coined the term “oximeter” in the 1940s[ 36 ] and it has been used ever since to indicate spectroscopic analysis of the ratio of oxy- and deoxyhemoglobin in tissue. Earlier, oximeters used visible light and red and blue filters to analyze the ratio of oxy- to deoxyhemoglobin, relying on the difference in color of these two compounds sometimes referred to as “chromophores”.

The early machines measured hemoglobin saturation in the blood just below the skin surface since visible light cannot penetrate tissue very far, but were surprisingly accurate for their simplicity. Though they were accurate, they could only provide information about capillary blood in the skin. It was not until the 1950s when Chance[ 8 ] advanced the concept of differential spectroscopy with NIR light in vivo and Jobsis in the 1970s[ 28 ] promoted its use for the estimation of hemoglobin saturation in tissue, which led to its practical clinical use becoming possible.

The spectra in Figure 1 show that while hemoglobin absorption at shorter wavelengths is strong, there is very little absorption by oxy- and deoxyhemoglobin in the NIR region.[ 43 ] Hemoglobin as well as myoglobin and the cytochrome enzymes absorb light at NIR wavelengths but expansion of the Y axis is necessary to see the absorption spectra. Once this is done, a reproducible and specific absorption curve is obtained as shown in Figure 2 .

Figure 1

Oxy- and deoxyhemoglobin absorption spectra in vitro, showing strong absorption peaks at several ultraviolet and visible wavelengths but little absorption at overtone (harmonic) wavelengths above 650 nm (5) (reproduced with permission)

Figure 2

NIR absorption curve for oxy- and deoxyhemoglobin, showing the isobestic point at 805 nm and the dominance of deoxyhemoglobin absorption at wavelengths below 805 nm. The ratio of the absorption at 810 and 730 nm gives a measure of % oxygen saturation

The extremely low level of absorption of NIR light by hemoglobin is the dominant factor in achieving accurate measurements, requiring low light intensity in order to avoid overwhelming the signal and a very low level of noise in the system to produce a high signal to noise ratio. While benchtop co-oximeters utilize multiple wavelengths to differentiate various dyshemoglobins in vitro, noise reduction remains the most important factor in improving accuracy and precision in vivo.

CLINICAL USE OF NEAR INFRARED SPECTROSCOPY

Near infrared spectroscopy (NIRS) has been used extensively over the past decade to monitor oxygen delivery to the brain and spine in adults, children and infants during cardiac and vascular surgeries. It has been shown to improve outcomes and prevent potentially catastrophic results from incidents such as accidental cannula misplacement.[ 7 12 14 19 38 51 ] Over the last several years, the use of NIRS to monitor both cerebral and somatic tissues in infants and children during cardiac surgery and in the intensive care unit (ICU) has grown steadily, contributing significantly to the management of hemodynamics.[ 2 5 16 22 31 42 ]

The accuracy of NIRS for monitoring brain O₂ delivery has been validated by comparison to internal jugular vein hemoglobin saturation (SijvO₂) levels reported in independent studies in adults, children and infants,[ 1 30 40 ] as well as in data submitted to the Food and Drug Administration (FDA) in support of product clearances.

There are a number of factors that need to be taken into account when validating the accuracy of any cerebral oximeter, including the significant incidence of gross anatomical variability of the vascular anatomy of the brain,[ 4 ] requiring placement of the sensor on the same side of the head as the jugular vein that was sampled. Compensation for skull and muscle is also essential and was developed from empirical observations of injection of indocyanine green dye in the internal and external carotid arteries,[ 26 ] ensuring that cerebral regional oxygen concentration (rSO₂) is specific for brain.

Furthermore, rather than relying on global hypoxia, which affects all tissues, validation of specificity requires alteration of O₂ delivery to that specific tissue. This was done for brain by altering partial pressure of carbon dioxide in the arterial blood (PaCO₂) levels to increase cerebral perfusion in normal adults[ 30 ] and by internal carotid artery occlusion in an animal model[ 50 ] as shown in Figure 3 . All physiologic parameters, including oxygen saturation of arterial blood (SpO₂), remained constant during these experiments, demonstrating the ability of NIRS to obviate occult changes in blood flow to the brain when all other clinical measures remain stable.

Figure 3

Rapid and dramatic C-rSO₂ response to bilateral occlusion of the internal carotid arteries in a 4.2 kg piglet anesthetized with isoflurane (INVOS 5100C). Blood pressure remained unchanged and SpO₂ was 100% for the entire experiment

The issues of accuracy and precision are essential components of analytical techniques and are requisites for validating any monitoring technology but are different from target physiologic values. While pulse oximetry measures the saturation of arterial blood (SpO₂) by monitoring the pulse interval and has a defined target value, tissue oximetry is a venous weighted measure and hence reflects the arteriovenous (AV) difference and the adequacy of oxygen delivery. Tissue oximetry provides a range of “normal” saturation that is associated with venous outflow which is patient specific and is known to have wide variability.[ 9 ]

Studies reporting SijvO₂ means and range in normal subjects and cardiac patients using co-oximetry of blood samples from the internal jugular vein[ 9 10 20 37 ] are consistent with cerebral rSO₂ values reported in the literature [ Table 1 ] and those obtained in a screen of normal ambulatory adults [ Figure 4 ].

Figure 4

Cerebral rSO₂ in normal, ambulatory adults (n = 226), showing the lack of impact of skin color and gender (INVOS 5100C) (IRB approved clinical study, 2008)

It is critical to understand the value and accuracy of rSO₂ to remember that it is venous weighted and hence responsive to all the physiologic factors that influence oxygen availability such as anatomical variability, hemoglobin dissociation, cardiac output, dyshemoglobinemias, blood pH, vascular permeability and metabolic demand, resulting in an AV difference. The greatest value of rSO₂ monitoring results from the fact that it is impacted by all these variables and, hence, unlike SpO₂, reflects the amount of O₂ that was actually available to, and consumed by, the tissues.

Independent studies in humans and validation data for FDA clearance as well as data from animal studies shown in Figure 5 have demonstrated a high level of accuracy and specificity of cerebral rSO_2.

Figure 5

Regression analysis of cumulative rSO₂ versus SijvO₂ values during hypocapnic challenge or carotid occlusion (n = 5) in normal term piglets anesthetized with isoflurane (r² = 0.9076)

Somatic monitoring presents a greater challenge since the NIR light penetrates potentially thick muscle and fascial layers when applied to the body surface, making shallow compensation essential to limit the impact of intervening tissues. Animal experiments have demonstrated that when the skin to organ distance is less than 1.4 cm with the INVOS system (INVOS 5100C, Somanetics Corporation, Troy, MI, USA), changes in flow to the organ are reflected in immediate and sensitive change in the rSO₂.

The rSO₂ response to occlusion of the renal artery, stopping flow to the kidney in isoflurane anesthetized piglet, is shown in Figure 6 and the rSO₂ response of the gut to occlusion of the superior mesenteric artery (SMA) is shown in Figure 7 . The responses can be seen to be tissue specific with the other monitored tissues not changing in response to occlusion.

Figure 6

Rapid and dramatic rSO₂ response to occlusion of the renal artery in a piglet anesthetized with isoflurane (INVOS 5100C). Blood pressure remained unchanged and SpO₂ was 100% for the entire experiment

Figure 7

Rapid and dramatic rSO₂ response to occlusion of the Superior mesenteric artery in a piglet anesthetized with isoflurane (INVOS 5100C). Blood pressure remained unchanged and SpO₂ was 100% for the entire experiment

The specificity of the response to organ ischemia enables somatic rSO₂ to be used as a measure of peripheral perfusion and oxygen delivery and has been demonstrated to be very sensitive to changes in organ blood flow.[ 25 50 ] The use of perirenal monitoring as an indicator of peripheral perfusion has been well established in hemodynamic management of infant and neonatal congenital heart patients in the operating room (OR) and ICU.[ 2 3 5 17 18 21 22 24 31 35 46 ]

Tissue oximetry is complex and highly informative but is not a standalone diagnostic. It is a valuable part of a differential diagnosis and has been shown to provide an early alert to occult hemodynamic changes not indicated by other physiologic parameters including arterial blood gases and mean arterial pressure.[ 21 ] The pioneering work of George Hoffman and the group at the Children’s Hospital of Wisconsin in the use of NIRS in congenital heart patients down to 1 kg has been successful in improving hemodynamic management, resulting in improved outcomes[ 29 ] in these patients.

The relationship between cerebral and somatic rSO₂ has been defined and reduced to practice in congenital heart surgery and the cardiovascular intensive care unit (CVICU) with the perirenal rSO₂ kept higher than cerebral to ensure adequate peripheral perfusion[ 47 ] where possible. Renal values for normal term infants are higher than cerebral values,[ 6 ] while preterm neonates have been reported to have renal values closer to cerebral rSO₂. Preterm gut rSO₂ is lower and more variable,[ 34 ] consistent with ultrasound studies of SMA flow in premature neonates.[ 41 ]

Cerebral saturation thresholds for intervention have been established in adults and neonates based on clinical[ 3 13 17 18 23 33 35 45 48 ] and animal[ 27 32 ] data indicating that significant neural damage can occur when cerebral rSO₂ is below 40% for more than 180 or 30 minutes, respectively. Though prolonged values below 40% should always be of concern, impact on outcome can be patient specific due to the potential for ischemic preconditioning.[ 44 ] As can be seen in Table 1 , a small percentage of normal adults have low jugular vein saturations without apparent physiologic deficits and 1.3% of the normal, ambulatory subjects included in Figure 4 had low C-rSO₂. Setting preoperative baselines has become an essential part of NIRS to ensure that the small percentage of patients with tolerated low saturations is managed properly.

The management of hemodynamics in neonates presents a significant challenge. Blood pressure is adjusted with pressors and inotropes to the gestational age, which is standard of practice in many NICUs but is not well substantiated in relation to outcome.[ 11 15 ] Tissue- and drug-specific rSO₂ response to pressors and inotropes has been reported,[ 39 ] demonstrating that simple targeting of pressure is not effective in guaranteeing adequate perfusion balancing between the brain and somatic organs.

The animal experiments cited above demonstrated drug specific responses in oxygen delivery between the brain and the kidney, gut and muscle, which would not be obvious from other clinical measures since the pressure and SpO₂ remained unchanged. Simple adjustment of the mean arterial pressure to improve circulation has the potential to expose patients to the risk of increased cerebral flow, potentially leading to intracranial bleeds or conversely to hypoxic conditions from vasoconstriction that could cause vascular or neuronal damage.

NIRS holds great promise for managing the impact of pressors and inotropes in infants and neonates to ensure that peripheral vasoconstriction or inotropic stimulation results in appropriate perfusion balancing and does not cause organ morbidities while resulting in too much or too little blood flow to the brain. Conversely, there will be situations where it is necessary to deny the visceral organs to provide enough O₂ to prevent neurological compromise despite the cost of organ damage. NIRS currently provides the only means of monitoring the distribution of perfusion in these instances.

While cerebral rSO₂ below 40% has been shown to present significant risk as discussed above, there is no target level rSO₂ for the organs. Multisite monitoring, however, provides insight into the tissue response to interventions allowing the clinician to asses the impact of those interventions on the distribution of blood flow.

In addition to hemodynamic management, NIRS can provide insight into potential cerebral perfusion response to changes in ventilation. Premature neonate’s lungs are frequently kept functional with high frequency ventilation or continuous positive airway pressure, both of which can impact PaCO₂ levels. Normal SpO₂ does not ensure appropriate oxygen delivery to the brain which is responsive to changes in circulating CO₂. C-rSO₂ reflects blood flow to the brain, and hence O₂ delivery, and responds rapidly to changes in PaCO₂ as shown in Figure 8 . Abrupt changes in C-rSO₂ following ventilation changes can be used to direct the clinician to run a blood gas to protect against unanticipated CO₂ change.

Figure 8

C-rSO₂ tracking of cerebral O₂ delivery response to hypercapnia followed by hypocapnia in a 2.0 kg, term, normothermic piglet, demonstrating the ability of NIRS to track the cerebral blood flow response to changes in CO₂ (CC flow, common carotid flow; MBP, mean blood pressure; etCO₂, end tidal CO₂). SpO₂ of 100% and blood pressure remained constant through the entire experiment. Periodic blood gas analysis was run to validate the etCO₂

CONCLUSIONS

Advances in the use of NIRS to determine cerebral and somatic oxygen delivery has provided a new and powerful tool for obviating frequently occult changes in oxygen biology that can result in serious morbidities and even death. The information provided by NIRS is a significant and unique addition to hemodynamic management and has been shown to improve the outcome and reduce the length of stay. While a threshold for cerebral rSO₂ has been established in children and adults, the use of somatic monitoring provides a new component to differential diagnosis and intervention. The inclusion of multisite rSO₂ in a diagnostic assessment provides insight into perfusion distribution and directs the clinician to assess the potential causes of change in cerebral or somatic O₂ delivery, enhancing patient management and improving outcomes.

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