Blood oxygen saturation is a clinically important diagnostic parameter, which provides valuable information for timely treatment of several pathological conditions e.g. sepsis, hypoxemia or decompression illness.
Traditional monitoring of saturation is performed in arterial blood as it provides transport of oxygen to the tissue. The gold standard for such non-invasive saturation detection is well known pulse oximetry technique-first proposed in the early 1930s. This method is easy to use and reliable in most ambulatory settings1. However it sometimes fails in emergency situation when monitoring critically ill patients. Another alternative is transcutaneous gas analysis in the tissue using Severinghaus and Clark type electrodes which provide information comparative to arterial blood2. This method is widely used in neonates monitoring because of its noninvasiveness, hence its reliability largely depends on tissue perfusion level, and in case of restricted or impaired skin microcirculation, pO2 value tends to be underestimated and pCO2 overestimated.
For this reason many invasive techniques were developed and presently available to clinicians. Most common operation principles are either use of lab-on-chip technology and at bedside in addition to saturation, measure blood gases, pH levels and electrolytes such as (iSTAT, Abbott) or utilize photo spectrometric approach and measure concentration of oxy and deoxy hemoglobin in the whole blood using absorption spectra (Avoximeter, Accriva Diagnostics). All of them have several inherent drawbacks-invasiveness with consequent risk of infections, and requirement of a relatively large blood sample, which is not an obstacle during arterial or venous blood measurement (sampling from the blood vessel with the syringe) but substantially limit application of methods in analysis of capillary blood from the skin. Moreover, all aforementioned techniques fail in providing local variation of blood saturation in the skin. Which is crucially important for assessment of cutaneous blood saturation in pathologies such as Raynaud’s disease and septic mottling – discoloration and purple patches on the skin over the knee, where heterogeneity of saturation play an important diagnostic role.
Recently, non-invasive contactless optical techniques are gaining acceptance in clinics as they provide information at bed-side without discomfort, risk of infection and requirements for expensive disposable supplies utilized in invasive procedures.
Hyperspectral imaging is among them and has already proven its clinical potential in detection of skin malformations3, however its use for skin blood oxygen saturation detection is still challenging because of structural non-uniformity of skin and complex cutaneous blood circulation4. Traditionally, development and evaluation of such methods require tissue phantom measurements; however even advanced phantoms still barely mimic the real skin with its complex microvasculature. Therefore, the most appropriate and realistic evaluation could be done under in-vivo conditions. While in-vivo tests are limited by several drawbacks, such as a pure control on desirable parameters, individual variance among subjects and requirements for a large and homogeneous subject group.
Therefore, the purpose of this present study was to develop in-vivo method for manipulation of skin oxygen saturation, and evaluate this approach by means of hyperspectral imaging assessing cutaneous blood oxygen saturation.
The present study was conducted in accordance with The Helsinki Declaration and approved by Ethics Committee of the University of Latvia. Prior to the study, every subject was informed about all procedures, particularly emphasizing on the possible discomfort during long occlusion and of blood sampling procedure from the fingers. Thirteen healthy subjects (25 ± 5 y.o., mean±SD) gave informed consent and were enrolled in the study.
To insure adequate microcirculation, the surface temperature of the right middle and index fingers was measured with a contactless thermometer (Raytech Inc.) and subjects with the skin temperature below 27°C, were excluded from the study because of reduced cutaneous blood flow and possibly compromised baseline skin saturation.
Before experimental procedure, subject was seated in a comfortable chair with supported hands. The entire protocol comprises four consecutive stages, see Fig.1.A. During the first stage, an intact finger (second index finger) was disinfected with isopropyl alcohol pad and pricked using finger picker (soft click, Accucheck). The small capillary blood sample (120uL) was collected using heparinized sampling tube (Accriva Diagnostics) and transferred to CG4+ cartridge for analysis with a portable whole blood analyzer (iSTAT, Abbott).
In order to produce alterations of skin capillary blood biochemical parameters and oxygen saturation, in the second stage of protocol the proximal phalanx of the right middle finger was occluded with a pneumatic cuff at the 150 mmHg pressure and kept occluded for 25 minutes.
Seemingly long finger arterial occlusion time is common in clinics and laboratory settings and not harmful to subjects. Performed as a routine during orthopedic operations; with the occlusion time around 2h and the cuff pressure 50 mmHg above patient systolic blood pressure. The recommended single occlusion time should not exceed 30 minutes for elderly and critically ill patients5, following the 3-5 min post-occlusion period prior to next occlusion6.
There are several papers describing normal physiological studies (healthy volunteers) with the limb occlusion up to 30 minutes at suprasystolic cuff pressure without any harm to subjects 7–10. Moreover, in our study, subjects were able to interrupt occlusion procedure at any moment.
In the third stage of protocol during the last minute (25th) of occlusion, the hyperspectral cube (HIS cube) from the hairy skin of both occluded (middle) and intact (index) finger was captured at 450nm-800nm range and 5nm spectral resolution with tunable filter hyperspectral camera, Nuance EX (CRi, UK) as depicted in Fig.1.B. The HIS cube acquisition procedure has been described in detail elsewhere11.
Within the minute after hyperspectral acquisition, capillary blood was collected from the occluded finger and analyzed by the same portable analyzer-fourth stage. After that, pneumatic cuff has been released and the finger returned to the normal state within the following 1-3 minutes.
The six tissue ischemia characterizing blood parameters were obtained from whole blood analyzer from intact and occluded finger: pCO2-carbon dioxide partial pressure, pO2-oxygen partial pressure, Lact-lactate concentration, pH-acidity, HCO3- bicarbonate concentration and SaO2- Hemoglobin saturation with the oxygen.
The processing of hyperspectral data
In the modeling process it has been assumed that skin consists of three layers: stratum corneum (SC), epidermis (epid.), and dermis (derm.). Another assumption was that SC does not absorb light, only providing scattering of the light as it contains mainly keratin. Epidermal layer has skin pigment melanin which absorbs light and the main absorber in the dermal layer is blood, which can be divided in absorption of oxy/deoxy-hemoglobin (HbO2 and HbD).
Accordingly, absorption coefficients are:
where Cmel, ChbO2, ChbD is chromophore concentration in skin, εmel, εhbO2, εhbD is extinction coefficients of melanin, HbO2 and HbD.
The scattering occurs in whole skin, each layer has different scattering properties. The model is sophisticated as the scattering depends also on absorption in skin chromophores14:
where µs500 is reference scattering at λ = 500nm, ρ, γ – scattering parameters. Attenuation coefficient is µ = µa+µs.
Using 3-layer light diffusion model, we obtain reflectance spectrum R(λ) of the model.
Reflectance depends on Cmel, ChbO2, ChbD and model parameters µs500sc, µs500epid, ρsc, ρepid, γsc, γepid and layers thicknesses. Chromophore concentrations are found fitting reflectance spectrum of the model to measured reflectance. Since model parameters can slightly deviate from expected , we allow change in these parameters within a small range using fitting.
The final skin microcirculation parameter is oxygen saturation (SaO2), which can be found from the following equation:
For off-line analysis of HSI data acquired by Nuance camera, image processing software was developed in the Matlab GUI environment (Fig. 2). This software allows visualization of oxygen saturation maps, mapping its distribution in different skin regions of different body parts. Computation of maps is performed by algorithmic steps described in our previous study 11.
The statistical analysis was performed using (SigmaPlot12, Systat Software) statistical software. The group values were expressed as the arithmetic mean ±standard deviation. To compare the group mean values, Student-t test was utilized, considering p<0.005 significance level. The comparison of methods (HIS vs REF blood analyzer) was performed utilizing Bland-Altman Analyses.
RESULTS AND DISCUSSION
Capillary blood biochemical parameters
The baseline values of capillary blood parameters in the intact finger were very similar for all subjects, displaying small standard deviation values, arithmetic mean ±standard deviation values are as follow: pCO2- 36.77±3.95 mmHg, pO2-74.20±5.97 mmHg, Lact-1.72±0.85 mmol/L, pH- 7.44±0.03, HCO3- 24.93±2.07mmol/L and SaO2- 95.13±1.46 %.
The obtained values were slightly lower than typical arterial values indicating normal metabolism, cardiopulmonary function and optimal cutaneous blood supply 1516. The obtained capillary blood hemoglobin saturation values were in the physiological range, hence slightly lowered in comparison to arterial blood.
Taking into the consideration sufficient cutaneous perfusion, as confirmed by skin temperature measurement, and relatively small volume of fingers, the values of these blood parameters can be attributed to the cutaneous circulation, which is partly determined by superficial vascular plexus situated in papillary dermis.
Similar baseline values for oxygen and carbon dioxide concentrations have been reported during transcutaneous gas measurement: tcO2=73.9±14.6 mmHg and tcCO2=40.5±9.8mmHg supporting our findings17. Our assumption is advocated by the observation of local differences between capillary blood values from different sites of the body18. The different tissue has different energetic metabolism, perfusion and capillary density19. The hands and fingers are unique as they have very high capillary density and majority of capillaries are situated in the skin papillary dermis (approx. 7 times difference in density to other body sites), close to the skin surface19. The dermis exhibits an extensive vasculature that is arranged in two layers that are parallel to the skin surface. The superficial plexus is situated between the papillary and the upper reticular dermis, while deep plexus in the lower reticular dermis, and are connected by perpendicularly orientated communicating vessels, the capillary loop rise upwards into the papillae from the subpapillary plexus20. The major determinant of cutaneous oxygen consumption is metabolism, which occurs in all layers of epidermis and dermis except stratum corneum. The oxygen demand is partially covered by the capillary blood supply and partly by diffusion from the atmosphere through the skin’s upper surface. In contrast, the epidermis has no vasculature, but is exposed directly to the atmosphere4.
Our approach on alteration of skin blood saturation is based on induction of hypoxia to the skin and underlying tissue by arresting blood supply, which should substantially change capillary blood parameters in occluded tissue. As expected earlier, twenty five minutes of finger arterial occlusion produced significant alterations of blood parameters proximally to occlusion site in all subjects, resembling blood gas profile seen in the clinics during severe acidosis and hypoxemia1521. The mechanism of occlusion is well known, as occlusion is utilized as a routine procedure during orthopedic surgery22–24. During arrested arterial blood supply and venous blood drainage, occluded tissue try to maintain metabolism resulting in utilization of blood oxygen and production of carbon dioxide. After diminishing oxygen reserves, tissue energetic metabolism switches to anaerobic, substantially increasing acidity and concentration of anaerobic byproducts. Finger occlusion produced significant alterations of capillary blood for all 13 subjects indicating acidosis and hypoxemia in the occluded region. The observed blood values were as follow: pCO2- 73.83±13.40 mmHg, pO2- 21.93±4.62 mmHg, Lact-6.60±1.22 mmol/L, pH- 7.24±0.09, HCO3- 23.20±2.28mmol/L and SaO2- 22.73±9.09 %, demonstrating larger dispersion of blood values in comparison to the baseline, possible because of different metabolic rate and size of the occluded tissue. Similar data has been obtained in occlusion in other studies, confirming our results24. The comparison of group mean values in intact and occluded finger capillary blood parameters are depicted in Figure 3.
The observed capillary blood changes in occluded region – occluded finger last for less than a minute, following release of occlusion cuff, without any harm to the subjects. Because of relatively short occlusion time, small occluded tissue volume and relatively high capacity of peripheral tissue (finger) to adapt for hypoxia25. The significant blood hemoglobin saturation drop has been achieved in the occluded finger as expected. Hence, occlusion influenced other undesirable blood parameters such as concentration of lactate, partial pressure of carbon dioxide and pH, which is considered as the side effect in our finger occlusion model, cannot be eliminated, due to the nature of physiological regulation mechanisms.
Skin hyperspectral parameters
During first minutes of occlusion, subjects felt slight discomfort which almost disappeared after 4-7 minutes following application of occlusion cuff and at the end of occlusion, the finger had reduced sensation. During the time course of occlusion, the restrained finger became darker, displaying signs of mild cyanosis. For some subjects was remarkable, due to the blood pooling in superficial vascular plexus situated in papillary dermis. It has been supported by our observation that mechanical compression of skin tissue produced white patches, as the capillary blood pools were dispersed. The typical cyanotic finger is depicted in Figure 4 on the left side, with the corresponding spectrum acquired from intact and occluded skin, pointing on the obvious difference in hemoglobin maximal absorption spectral region 500-600nm.
In order to hyperspectrally evaluate the reliability of finger occlusion model, an assumption that oxygen is distributed uniformly in occluded tissue region has been made, which is the matter of discussion and controversies in the literature.
The mean baseline value for intact skin saturation acquired by the blood analyzer was 95.13±1.46 %, which resembles arterial blood. Controversial data have been reported in the literature regarding baseline values of skin capillary blood saturation which were recorded with hyperspectral imaging-ranging from 50%-96%26–31.
The diffusion of gases within relatively small tissue volume depends on many factors such as tissue temperature, gas concentration gradient and tissue mechanical composition, and within 25 minutes should lead to equal distribution of oxygen in skin and underlying soft tissue. Therefore it has been assumed that skin saturation values are represented by saturation of capillary blood taken from the skin microvasculature. The group mean value for HIS derived SaO2 in intact finger skin was 89.46±8.79%, while substantially decreasing in occluded finger: 25.85±14.00%, displaying small difference between two independent techniques, as seen in Figure 5.
The HIS derived mean saturation value display substantially higher dispersion compared to the referent saturation (standard deviations) indicated on possible differences of skin structure or capillary density across the subjects as the tissue model parameters remained the same.
The obtained skin blood oxygen saturation values were similar for the whole blood analyzer and hyperspectral imaging technique, indicating the reliability of our proposed finger arterial occlusion model. However, further studies are required to improve reproducibility of occlusion induced saturation changes and quantify skin thickness to improve accuracy of utilized tissue diffusion model.
This work was supported by the European Regional Development Fund project #126.96.36.199/16/A/065 “Optical Non-invasive Hybrid Method for Early Diagnostics and Therapy Guidance in Sepsis”.
Schmidt, S., Langner, K., Dudenhausen, J. W. and Saling, E., “Reliability of transcutaneous measurement of oxygen and carbon dioxide partial pressure with a combined Po2-Pco2 electrochemical sensor in the fetus during labor.,” J. Perinat. Med. 13(3), 127–133 (1985). 10.1515/jpme.19188.8.131.52Google Scholar
Diebele, I., Kuzmina, I., Kapostinsh, J., Derjabo, A. and Spigulis, J., “Melanoma-nevus differentiation by multispectral imaging,” Proc. SPIE-OSA Biomed. Opt., N. Ramanujam and J. Popp, Eds., 80872G–80872G-6 (2011).Google Scholar
Lenasi, H., “Assessment of Human Skin Microcirculation and Its Endothelial Function Using Laser Doppler Flowmetry,” [Medical Imaging], F. Okechukwu Erondu, Ed., InTech, 412 (2011).Google Scholar
Horlocker, T. T., Hebl, J. R., Gali, B., Jankowski, C. J., Burkle, C. M., Berry, D. J., Zepeda, F. A., Stevens, S. R. and Schroeder, D. R., “Anesthetic, patient, and surgical risk factors for neurologic complications after prolonged total tourniquet time during total knee arthroplasty.,” Anesth. Analg. 102(3), 950–955 (2006). 10.1213/01.ane.0000194875.05587.7eGoogle Scholar
Thijssen, D. H. J., Kooijman, M., de Groot, P. C. E., Bleeker, M. W. P., Smits, P., Green, D. J. and Hopman, M. T. E., “Endothelium-dependent and -independent vasodilation of the superficial femoral artery in spinal cordinjured subjects.,” J. Appl. Physiol. 104(5), 1387–1393 (2008). 10.1152/japplphysiol.01039.2007Google Scholar
Saknite, I., Grabovskis, A., Kazune, S., Rubins, U., Marcinkevics, Z., Volceka, K., Kviesis-Kipge, E. and Spigulis, J., “Novel hybrid technology for early diagnostics of sepsis,” Proc. SPIE 10057, 100570F (2017).Google Scholar
Spott, T., Svaasand, L. O., Anderson, R. E. and Schmedling, P. F., “Application of optical diffusion theory to transcutaneous bilirubinometry,” Proc. SPIE 3195, 234–245 (1998).Google Scholar
Chin, M. S., Freniere, B. B., Lo, Y.-C., Saleeby, J. H., Baker, S. P., Strom, H. M., Ignotz, R. a., Lalikos, J. F. and Fitzgerald, T. J., “Hyperspectral imaging for early detection of oxygenation and perfusion changes in irradiated skin,” J. Biomed. Opt. 17(2), 26010 (2012). 10.1117/1.JBO.17.2.026010Google Scholar
Huang, J., “Multispectral Imaging of Skin Oxygenation” (2012).Google Scholar