Utilization of indocynanine green fluorescent imaging (ICG-FI) for the assessment of microperfusion in vascular medicine

Cardiac surgery

Intraoperative assessment of graft patency and detection of significant coronary artery bypass stenosis is of major importance for optimal early and long-term outcome following coronary artery bypass grafting (CABG).

However, no routine quality control is performed by most cardiac surgeons because the techniques used suffered from time-consuming, unreliable, invasiveness, or lack of visualization.

FCI using the dye ICG is a non-invasive imaging technology for intraoperative visualization of coronary vessels and myocardial perfusion and can detect patency of the bypass graft as well as graft occlusion [3], [4], [5], [6], [7]. Several studies demonstrated that the FCI technique was clinically useful for evaluation of graft patency using a similar ICG-based imaging device (SPY; Novadaq Technologies; Toronto, Canada) for quality control after CABG [3], [4], [5], [6]. Solely visual assessment of non-occlusive graft-flow abnormalities could not be identified reliably [3], [4], [8]. Therefore, additional quantitative assessment of myocardial perfusion by FCI is a useful tool for intraoperative quality control.

Figure 1:

Indocyanine green fluorescent imaging (IDG-FI): After intravenous injection, the region of interest is illuminated with near-infrared light (785 nm).

The fluorescence emission of the excited dye is detected by an infrared-sensitive charge-coupled device camera system (dynamic range 54 dB) equipped with a band pass filter for the selective transmission of light at the emission maximum of ICG (830 nm).

Quantitative assessment of myocardial perfusion during coronary stenosis of variable severity was validated in an experimental setting [9], [10], [11]. For FCI, ICG (0.01 mg/kg body weight) is intravenously applied through a peripheral venous line and the heart is illuminated with near-infrared light at a wavelength of 785 nm with a total output of 80 mW in a field of view of 10 cm in diameter (1 mW/cm²) operating at a distance of 20 cm above the left ventricle. The fluorescence emission of the excited dye was detected by an infrared-sensitive charge-coupled device camera system (dynamic range 54 dB) equipped with a band pass filter for the selective transmission of light at the emission maximum of ICG (830 nm; Figure 2). The FCI images were recorded in real-time and analyzed using a digital image processing system as previously described (LLS GmbH, Ulm, Germany) [9], [10], [11].

Figure 2:

Left: experimental setting of ICG-FI.

The tissue in the region of interest is illuminated with near-infrared light at a wavelength of 785 nm with a total output of 80 mW in a field of view of 10 cm in diameter (1 mW/cm²) operating at a distance of approximately 20 cm above tissue. The fluorescence emission of the excited dye is detected by an infrared-sensitive charge-coupled device (CCD) camera system (dynamic range 54 dB). Right: ICG-FI before stenosis (above) and myocardial perfusion during flow-limiting coronary stenosis of high severity (lower).

The experimental study was able to show that quantitative assessment of myocardial perfusion during flow-limiting coronary stenosis of high severity and even during non-flow limiting stenosis is possible by FCI (Figure 2).

Nevertheless, the experimental studies were evaluated under perfectly controlled hemodynamic conditions in open-chest pigs. Direct transfer of the experimental findings into a clinical setting in humans might be limited: rotation of the heart is necessary for proper imaging of the lateral or posterior wall. Changes in hemodynamic parameters such as heart rate, blood pressure, and cardiac output as well as optical parameters like scattering due to overlying fat tissue and movement of the beating heart may influence absolute values. Furthermore, in a clinical setting, competitive coronary flow and collateral flow may affect perfusion measurements, which have to be proved in future studies.

Finally, FCI might be a useful tool for intraoperative quality control during CABG.

Vascular surgery

Peripheral arterial disease (PAD) is a major health problem affecting over 200 million people worldwide [12]. Demographic changes inevitably lead to increasing numbers subsequently requiring an optimal best medical or invasive treatment. As the gold standard Ankle-brachial index (ABI) measurement is certainly the oldest method for diagnosis of PAD and assessment of lower limb macroperfusion [13]. However, its utilization is limited in patients with extensive calcification of the medial vessel layer causing incompressibility of peripheral arteries during measurement leading to falsely elevated pressure values. Other measuring tools, such as toe-pressure brachial index measurements (TBI), photoplethysmography, and transcutaneous oxygen pressure measurements (TcPO2), are used for assessing microperfusion of the foot [14], [15]. However, their application requires sensors or probes being placed on the foot to conduct microperfusion measurements. Hence, usability may be limited in patients with foot ulcers and infected tissue. Furthermore, diabetes mellitus poses a significant risk factor for disturbing the micro-circulation of the lower extremity leading to diabetic foot ulcers with increasing incidence and prevalence that may contribute to increasing numbers of amputations [16]. As described above, ICG-FI serves as a tool for assessing the microperfusion of various tissues without necessary probes that have to be placed on the area of interest. For that purpose, it has been widely used in various medical disciplines over the 30 years with excellent results in terms of validity and reproducibility [9], [17], [18], [19], [20], [21]. Considering the advantages of this technique, it might be surprising that its utilization for the assessment of mirco-circulation in PAD is relatively new. Braun et al. and Colvard et al. successfully tested ICG-FI (SPY system, NOVADAQ, Bonita Springs, USA) as a tool for quality control by evaluating the perfusion of the foot in patients with PAD prior and after a revascularization procedure [22], [23]. Quantitative evaluation of data was performed via the SPY software-package assessing time-intensity curves of fluorescent intensity by ingress, ingress rate, egress, and egress rate. Results were successfully correlated to ABI and Toe-pressure measurements (TP). Igari et al. correlated results of pre- and postoperative ICG-FI to ABI, TBI, and TP [24]. They were the first in assessing different regions of interest (ROIs) of the foot and described “time from ICG onset to maximum intensity” (Tmax), time elapsed from fluorescence onset to half the maximum intensity” (T1/2) and “fluorescence intensity measured 10 seconds after the onset of fluorescence” (PDE10) as new parameters used for the assessment of curves obtained from ICG-FI. They found Tmax and T1/2 more significantly correlated with ABI, TBI, and TP [24]. In another study, Venermo et al. showed repeatability of time-intensity curves obtained from ICG-FI using T1/2 and PDE10 in patients undergoing a revascularization procedure. Interestingly a strong correlation of TcPO2 and PDE10 for diabetic patients was observed [25]. Although the process of ICG-FI measurements of the foot may vary between the different studies, the main principle stays the same. Our protocol and setting for ICG-FI measurements can be obtained from Table 1 and Figure 3. In a recently published study, we introduced a new way of assessing time-intensity curves obtained from ICG-FI in patients that underwent open-surgical revascularization procedure for PAD [26]. Time-intensity curves were analyzed offline using our own software package (Institute for Laser Technology, University Ulm, GmbH) that enables manually fitting the slope of fluorescence intensity (SFI) to the maximum incline of the curve (Figure 4) [26]. Since results obtained from maximum fluorescent intensity measurements, which are analyzed by many previous studies, can be influenced by skin color, light in the room, distance to the camera, peripheral edema, and previous injections of ICG causing a residual fluorescent signal may in our opinion over or underestimate perfusion. We successfully correlated results to perfusion measurements obtained from ABI and photoplethysmography and thereby proved the practical feasibility of this new technique of analyzing data [26]. ICG-FI can be utilized for various purposes in vascular medicine. Rother et al. recently used ICG-FI for assessing indirect and direct revascularized angiosomes after tibial bypass surgery [27]. Lepow et al. showed first attempts in using the ICG-FI to visually assess a chronic diabetic ulcer and intraoperatively evaluated wound margins during debridement in the operating room [28]. They concluded that ICG-FI may serve as a tool for predicting wound healing and help in determining resection margins during surgical treatment of chronic wounds. Figure 5 presents a patient suffering from microembolization of digitus I of the left foot, which was caused by atrial fibrillation without sufficient anticoagulation (Figure 5). Visual assessment of the bare foot and the image obtained from ICG-FI consistently proved full recovery after medical treatment with heparin and Alprostadil (Prostavasin) for 10 days.

Figure 3:

Setting for ICG-FI measurements.

The camera is positioned perpendicular to area of interest. ICG-FI is captured when all light sources are removed.

Figure 4:

Green time-intensity curve corresponding to preoperative ICG-FI measurement.

Purple time-intensity curve corresponding to postoperative ICG-FI measurement. Yellow line (linear regression trendline) corresponding to SFI manually fitted to the maximum incline of the curves. Reprinted from Publication Vasa, 46/5, H. C. Rieß et al., A new tool for fluorescent imaging, pp. 383–388. Copyright Hogrefe Publishing Corp. Reproduced with permission.

Figure 5:

Microembolization of digitus I of the left foot.

Before (left side) and after 10 days of treatment with Heparin and Alprostadil (Prostavasin).

Visceral surgery

Intestinal microperfusion and viability of intestinal organs is usually estimated from the color of serosal surface, presence of peristalsis, pulsation, and bleeding from marginal arteries. However, clinical assessment remains subjective and still depends on the personal experience of the surgeon [29]. ICG-FI is getting more and more common to evaluate tissue perfusion because of its impact in anastomotic healing [30], [31], [32]. However, the method still remains subjective caused by solely visual interpretation of fluorescence intensity as a parameter of perfusion. Our study group recently evaluated the role of FI for quantitative assessment of intestinal perfusion first in a gastric tube model as a one-vessel model and second in an experimental setting of mesenteric ischemia.

Although numerous objective quantitative techniques of intraoperative bowel viability assessment are available, fluorescence based methods seem to be most promising [29], [33]. Several studies describe clinical use of ICG-FI in esophageal [32], [34], [35], [36], [37] and colorectal surgery [31], [38], [39], [40], [41], [42], [43], [44], [45], [46].

Zehetner et al. concluded in their study on 150 patients undergoing esophagectomy, that intraoperative real-time assessment of perfusion correlated with the likelihood of an anastomotic leak and confirmed the critical relationship between good perfusion and anastomotic healing [35]. Same observation has been recently published by Karampinis et al. presenting the results in 55 patients [32]. However, only visual and no quantitative assessment of the ICG-FI data was performed.

Toens et al. conducted an experimental study on mesenteric ischemia in a rabbit model comparing ICG-FI to radioactive microspheres. Validation of ICG-FI was performed by the increment of fluorescence in the ischemic ROIs compared to a control loop as reference region. ICG-FI was concluded to be a feasible, reliable, and valid technique for mesenterial blood flow assessment [47].

Diana et al. showed in a porcine study the real-time assessment of intestinal viability using ICG-FI. Quantitative assessment of ICG-FI was reached by calculating the time to peak in ischemic and non-ischemic areas of the bowel. They concluded that ICG-FI perfusion assessment may effectively detect bowel perfusion [33]. They concluded in a following study that 25% less perfusion certainly impairs anastomotic healing without generating surgical complications [48].

In our studies (manuscript under submission), ICG-FI correlated perfectly with the predicted perfusion changes using the explained evaluation tool SFI, BSFI, and TTS. In our one-vessel model, we found a strong correlation between our evaluation technique, and the fluorescent microspheres as the gold standard in experimental perfusion assessment.

The aim of our second study was to establish and validate our quantitative assessment tools for intraoperative perfusion measurement in ischemic and post-ischemic bowel (Figure 6). Acute mesenteric ischemia remains a highly morbid condition with poor outcome [49]. It is mandatory to confirm diagnosis, assess bowel viability, perform revascularization if useful, and resect non-viable bowel as early as possible. Evaluation of bowel vitality is still subjective, and may lead to resection of segments that potentially can recover [49]. Thus, objective non-invasive methods to assess intestine viability are needed to determine correctly the extent of ischemia and to evaluate anastomosis in several visceral procedures.

The use of ICG-FI in evaluation of ischemic bowel has been described in small case series so far [46], [50], [51], [52]. All authors conclude that ICG-FI is easy to handle and little time-consuming even in emergency situations [46]. Some changed their intraoperative decision after assessing bowel perfusion via ICG-FI, still with the limitation of only subjective visual evaluation [46], [52]. Behrendt et al. investigated bowel perfusion after simple manual manipulation using ICG-FI in a rat model using a perfusion index between region of interest and AMS as reference region. They proved the system capable on quantifying gastrointestinal transit and bowel perfusion [53].

Matsui et al. performed similar experiments in a porcine model combined with a survivor study in rats. He used 30 min of ischemia to induce ischemia in 2–12 cm of bowel. ICG-FI was quantified by absolute fluorescence intensity and contrast-to-background ratio. They assumed that clinical assessment alone had high sensitivity, but relatively low specificity, and therefore accuracy remained low in predicting animal survival. Surprisingly, the quantitative metrics like maximum fluorescence intensity to control were only marginally better than clinical assessment [54].

Our study evaluated the use of ICG-FI in the assessment of bowel viability after different ischemic periods in a porcine model. In contrast to existing studies, ischemic period was adjusted to realistic clinical setting. ICG-FI showed significant difference in tissue viability comparing 6 and 10 h of ischemia. While macroscopic damage of bowel tissue after 10 h of ischemia was obvious even by solely visual inspection, detection of tissue damage after 6 h of ischemia remained difficult. Thus, quantitative ICG-FI can predict tissue damage even if qualitative macroscopic evaluation fails (Figure 5).

In connection with this work, we observed two major points, which affect the interpretation of the ICG-FI technique in daily life visceral surgery.

Figure 6:

Induced mesenteric ischemia in a porcine model on the left.

On the right side, the corresponding ICG-FI picture with total loss of fluorescence in the left loop.

Hyper intensity due to capillary leakage and thus the pooling of ICG in the tissue may lead to misinterpretation. In the case of visual assessment alone, there is a risk that previously damaged areas will be assessed as adequately perfused because of the ongoing fluorescence of the tissue. Normally, this pooling fluorescence lasts longer due to the loss of epithelial integrity. A well-perfused tissue shows a quickly influx of ICG, and a slower, but visible, outflow.

Hemodynamic alterations during operation or in between the patients causes different ICG-FI. In our studies we observed that higher cardiac causes elevated ICG-FI levels. Hemodynamics, such as cardiac output, blood pressure, and vascular resistance, volume load, and catecholamine substitution can influence ICG-FI results. In the clinical setting, those parameters have to be taken into consideration for valid measurement. If a stable setting is not possible, either a ratio to a baseline value, or comparison to a non-ischemic area during the same measurement is mandatory. So far, this important influencing factor seems to be underestimated in the literature.

SFI and BSFI measurements are valid quantitative assessment tools using ICG-FI for intraoperative quality evaluation of tissue perfusion. The translation to clinical use is therefore much easier and will be performed in the future. First observational studies in humans are mandatory to evaluate predictive value of ICG-FI assessment.