Integration of inspiratory and expiratory intra-abdominal pressure: a novel concept looking at mean intra-abdominal pressure
Annals of Intensive Care volume 2, Article number: S18 (2012)
The intra-abdominal pressure (IAP) is an important clinical parameter that can significantly change during respiration. Currently, IAP is recorded at end-expiration (IAPee), while continuous IAP changes during respiration (ΔIAP) are ignored. Herein, a novel concept of considering continuous IAP changes during respiration is presented.
Based on the geometric mean of the IAP waveform (MIAP), a mathematical model was developed for calculating respiratory-integrated MIAP (i.e. ), where 'i' is the decimal fraction of the inspiratory time, and where ΔIAP can be calculated as the difference between the IAP at end-inspiration (IAPei) minus IAPee. The effect of various parameters on IAPee and MIAPri was evaluated with a mathematical model and validated afterwards in six mechanically ventilated patients. The MIAP of the patients was also calculated using a CiMON monitor (Pulsion Medical Systems, Munich, Germany). Several other parameters were recorded and used for comparison.
The human study confirmed the mathematical modelling, showing that MIAPri correlates well with MIAP (R2 = 0.99); MIAPri was significantly higher than IAPee under all conditions that were used to examine the effects of changes in IAPee, the inspiratory/expiratory (I:E) ratio, and ΔIAP (P < 0.001). Univariate Pearson regression analysis showed significant correlations between MIAPri and IAPei (R = 0.99), IAPee (R = 0.99), and ΔIAP (R = 0.78) (P < 0.001); multivariate regression analysis confirmed that IAPee (mainly affected by the level of positive end-expiratory pressure, PEEP), ΔIAP, and the I:E ratio are independent variables (P < 0.001) determining MIAP. According to the results of a regression analysis, MIAP can also be calculated as
We believe that the novel concept of MIAP is a better representation of IAP (especially in mechanically ventilated patients) because MIAP takes into account the IAP changes during respiration. The MIAP can be estimated by the MIAPri equation. Since MIAPri is almost always greater than the classic IAP, this may have implications on end-organ function during intra-abdominal hypertension. Further clinical studies are necessary to evaluate the physiological effects of MIAP.
The intra-abdominal pressure (IAP) is an important clinical parameter with major prognostic impact [1, 2]. An unrecognised pathological increase in IAP eventually leads to intra-abdominal hypertension (IAH) and abdominal compartment syndrome (ACS) [3, 4], which result in significant morbidity and mortality . Thus, recognition and reliable measurement of IAP are the first important steps for prevention and management of IAH and ACS in critically ill patients .
Assuming no respiratory movement, the IAP would be relatively constant and primarily determined by body posture and anthropomorphy (e.g. body mass index) [3, 7]. The IAP may be affected by conditions influencing intra-abdominal volume and abdominal compliance (C ab) [3, 8, 9]. Further, the complex interaction between intra-abdominal volume and C ab during respiration (Figure 1) may significantly  and frequently (12 to 40 changes per minute) change the IAP (Figure 2), with more intense effects during positive-pressure mechanical ventilation or the presence of positive end-expiratory pressure (PEEP) [10–12].
According to the current consensus definitions of the World Society of the Abdominal Compartment Syndrome (WSACS), the IAP should be measured at end-expiration (IAPee) , referred to as the 'classic IAP' throughout the text. However, the IAPee is only a single component of an ever-changing trend and thus does not incorporate a considerable portion of this IAP trend (Figure 2). The objectives of this study were to develop and validate a novel IAP measurement concept to consider IAP changes during respiration and to identify independent variables influencing IAP within this novel concept.
Part A: mathematical model
A set of numerous IAP values occurs for a patient during a single respiratory cycle. The central tendency of a set of values can be calculated by the mathematical function of the 'mean'. In determining the mean IAP, the arithmetic mean for IAPee and the end-inspiratory IAP (IAPei) was described previously , calculated by dividing the sum of the values by the number of values. However, employing the arithmetic mean for the IAP waveform is mathematically incorrect. Instead, the mean of a waveform can be calculated by the 'geometric mean' function. The geometric mean is calculated by dividing the area under the waveform in a definite interval (i.e. the definite integral of the waveform) by the value of the definite interval . Therefore, the mean IAP (MIAP) for a sample IAP waveform between the times (T 0) and (T) in Figure 2 can be calculated as follows:
where 'MIAPri' is the respiratory-integrated MIAP, 'T−T 0' is the time interval for a full respiratory cycle, and 'IAP (t) dt' is the IAP at each time point (t). The result would be a time-weighted mean for the IAP waveform. This is closely analogous with the critically important cardiovascular concept of mean arterial blood pressure [16–18], which is the geometric mean of the arterial blood pressure waveform [19, 20]. Equation 1 may be simplified as follows (see the addendum):
where 'i' is the decimal fraction of the inspiratory time in a respiratory cycle and can be calculated from the inspiratory/expiratory (I:E) ratio (i = I /(I + E); 0 <i < 1) and ΔIAP = IAPei − IAPee. Since IAPee, i, and ΔIAP can be assumed to be independent, a computerised iteration can be used for a set of values for each parameter to determine their effect on MIAPri and to compare the MIAPri with the classic IAP.
The effects of IAPee on MIAPri and the classic IAP were examined through a gradual increase of IAPee from 12 to 25 mmHg, with steps of 1 mmHg (Figure 3). For each IAPee, a range of possible MIAPri values was calculated according to Equation 2 with an I:E ratio of 4:1 and an ΔIAP of 8.16 mmHg for the maximum MIAPri, and an I:E ratio of 1:4 and an ΔIAP of 1 mmHg for the minimum MIAPri. Because previous studies have shown a correlation between ΔIAP and IAPee, the ΔIAP was increased 10% for each 1 mmHg increase in the IAPee.
The effects of the I:E ratio on MIAPri and the classic IAP were examined by a gradual increase in the I:E ratio from 1:4 to 4:1 with steps of 0.5 (Figure 4). The amount of IAPee was held constant (19 mmHg). For each I:E ratio, a range of possible MIAPri values was calculated with an ΔIAP of 7 mmHg for the maximum MIAPri and an ΔIAP of 2 mmHg for the minimum MIAPri.
The effects of ΔIAP on MIAPri and the classic IAP were examined by a gradual increase in ΔIAP from 1 to 5 mmHg, with steps of 0.5 mmHg (Figure 5). The amount of IAPee was held constant (19 mmHg). For each ΔIAP, a range of possible MIAPri values was calculated with an I:E ratio of 4:1 for the maximum MIAPri and an I:E ratio of 1:4 for the minimum MIAPri.
Part B: human pilot study
In six ICU patients that were mechanically ventilated with Evita XL ventilators (Draeger, Lubeck, Germany), the mean IAP was automatically calculated as the geometrical mean (MIAP) via a balloon-tipped nasogastric tube connected to a CiMON monitor (Pulsion Medical Systems, Munich, Germany). The MIAPri was also calculated according to Equation 2. Data were collected on respiratory settings, plateau and mean alveolar pressures (P plat, P mean), PEEP, and dynamic compliance (calculated as the tidal volume (TV) divided by (P plat - PEEP)). The C ab was calculated as TV divided by ΔIAP. The thoraco-abdominal index of transmission (TAI) was calculated as ΔP alv (= P plat − PEEP) divided by ΔIAP, in which P alv is the alveolar pressure.
The effects of IAPee on MIAPri were examined by a gradual increase in PEEP from 0 to 15 cmH2O, with steps of 5 cmH2O during a best-PEEP manoeuvre (20 measurements at each PEEP level in five patients, resulting in 80 measurements). The effects of ΔIAP on MIAPri were examined by a gradual increase in TV from 250 to 1,000 ml, with steps of 250 ml during a low-flow pressure-volume loop (20 measurements at each TV level in five patients, resulting in 80 measurements). The effects of I:E ratio on MIAPri were examined by a gradual increase in the I:E ratio from 1:2 to 2:1, with steps of 0.5 during a recruitment manoeuvre (9 measurements at each I:E ratio in one patient, resulting in 45 measurements).
Statistical analysis was performed using SPSS software. Pearson correlation analysis and Bland and Altman analysis were performed. For comparisons between MIAPri and IAPee at different levels of IAPee (PEEP), TV, and I:E ratio, a two-tailed paired Student's t-test was performed. Data are expressed as the mean with the standard deviation (SD), unless specified otherwise. A P value below 0.05 was considered statistically significant. The local EC and IRB approved the study, and informed consent was obtained from next of kin.
Part A: mathematical modelling
According to Equation 2, three major independent parameters determine the MIAPri: IAPee, I:E ratio, and ΔIAP. Therefore, for each IAPee, the MIAPri depends on two other factors (Figure 3). For IAPee values between 16 and 20 mmHg, the classic IAP remained below the ACS threshold (dashed line in Figure 3); however, the MIAPri was able to exceed the ACS threshold. Furthermore, as seen in Figures 4 and 5, the classic IAP was continuously below the ACS threshold, but different ranges of probable MIAPri values were above the ACS threshold. By changing the I:E ratio, the MIAPri values changed with dissimilar intensities (e.g. when the I:E ratio decreased from 4:1 to 3.5:1, the intensity of changes in the MIAPri values was less than that when the I:E ratio decreased from 1.5:1 to 1:1; Figure 4). Furthermore, for a constant IAPee, higher values for either the I:E ratio or ΔIAP were found to be capable of causing a wider range of possible MIAPri values (Figures 4 and 5). Mathematically, for all instances in which the ΔIAP was greater than 0 mmHg, the MIAPri was larger than the classic IAP (see the addendum) .
Part B: human pilot study
Six mechanically ventilated patients (three severely burned patients and three surgical ICU patients) were studied. The male-to-female ratio was 2:1. Table 1 summarises the baseline patient demographics.
Regression analysis and Bland and Altman analysis
In total, 205 paired MIAP and MIAPri measurements were performed with an identical statistical mean of 12.2 ± 3.8 mmHg. Figure 6A shows an excellent correlation between the MIAP and MIAPri (R2 = 0.99, P < 0.001). Analysis according to Bland and Altman showed a bias and precision of 0 and 0.2 mmHg, respectively, with small limits of agreement ranging from −0.4 to 0.5 mmHg (Figure 6B). The percentage error was 3.5%.
Effect of IAPee, I:E ratio, and ΔIAP on MIAPri
Gradually increasing PEEP from 0 to 15 cmH2O resulted in an increase in MIAPri from 11.7 ± 4.1 to 13.1 ± 4.2 mmHg (P < 0.001). Meanwhile, IAPee increased from 9.9 ± 3.4 to 11.9 ± 3.7 mmHg (P < 0.001). Moreover, a gradual increase in the I:E ratio from 0.5 (1:2) to 2 (2:1) caused an increase in MIAPri from 10.8 ± 2.6 to 12.9 ± 2.9 mmHg (P < 0.001), while IAPee increased from 9.7 ± 2.3 to 10.4 ± 2.5 mmHg (P < 0.001). In addition, gradually increasing TV from 250 to 1,000 ml led to an increase in ΔIAP from 2.1 ± 1.1 to 5.7 ± 2.3 (P < 0.001). This increase in ΔIAP resulted in an increase in MIAPri from 11.6 ± 4 to 13.1 ± 4.3 mmHg (P < 0.001), while IAPee increased from 10.7 ± 3.6 to 10.9 ± 3.5 mmHg (P = NS). The MIAPri was significantly higher than IAPee at each PEEP level, I:E ratio, and TV (Figure 7A,B,C; P < 0.001).
The classic IAP of patients was below the IAH grade I threshold; however, the MIAPri significantly exceeded the threshold in several instances (P < 0.001; Figure 7).
Univariate Pearson regression analysis showed significant correlations between MIAPri and IAPei (R = 0.99), IAPee (R = 0.99), ΔIAP (R = 0.78), and C ab (R = −0.74); between IAPei and IAPee (R = 0.96), ΔIAP (R = 0.86), and C ab (R = −0.73); between IAPee and ΔIAP (R = 0.7) and C ab (R = −0.73); between ΔIAP and ΔP alv (R = 0.79) and C ab (R = −0.58); and finally between TAI and C ab (R = −0.8) (P < 0.001). Figure 8A,B,C shows some regression plots.
Multivariate regression analysis
Analyses showed that the IAPee (mainly affected by PEEP), ΔIAP, and I:E ratio were independent variables defining the MIAP (Table 2). According to the regression analysis in our sample population, the MIAP can also be calculated from the following simplified formula (P < 0.001), in which 'I' and 'E' are elements of the I:E ratio:
A novel concept of IAP measurement based on the geometric mean of the IAP waveform was presented. The independent parameters determining the IAP in this concept were defined. The human pilot study validated the mathematical modelling with an excellent correlation. A significant difference was observed between the classic IAP and the MIAPri in our clinical study.
The human study confirmed that MIAPri is as accurate as an automated geometric MIAP calculation by a CiMON monitor. More importantly, the higher the MIAP or IAPee, the higher the ΔIAP since ΔIAP acts as an indirect marker of C ab. The ΔIAP is correlated with ΔP alv or is thus inversely correlated with dynamic compliance. As well, the higher the C ab, the lower the TAI. The human study confirmed the predictions of the mathematical modelling in which IAPee (affected by different PEEP settings), ΔIAP, and I:E ratio were recognised as the major independent determinants of MIAPri. We also showed that in patients with IAH and under mechanical ventilation, the IAP may be influenced by ventilator settings.
The critical difference between the MIAPri and the classic IAP near the ACS threshold in our mathematical modelling, as well as the significantly higher MIAPri than the IAPee around the IAH threshold in our human study, calls for future studies. The dissimilar intensity in MIAPri changes under changes in the I:E ratio in Figure 4 may implicate the existence of critical points in the I:E ratio, wherein changing this ratio may cause a more intense change in the MIAPri. Furthermore, since MIAPri seems to be almost always larger than the classic IAP, relying only on the classic IAP may place some patients at risk of silent IAH or ACS. Although the aim of the current study was not to address these implications clinically, these findings indicate that further investigations should be performed on respiratory manoeuvres to manage IAH in mechanically ventilated patients (e.g. decreasing the I:E ratio and/or the ΔIAP, or maintaining the I:E ratio in a predefined range).
A limitation of our study was the lack of data to evaluate the physiological difference between the MIAPri and the classic IAP. However, this study only aimed to prove the concept and to set the stage for further studies. Therefore, we believe that the lack of physiological data does not limit our findings. Nonetheless, further studies on the clinical effects of this concept are necessary before it can be introduced in clinical practice.
A novel concept MIAPri was presented to consider the IAP changes during respiration and was based on the geometric mean (MIAP) of the IAP waveform. An excellent correlation was observed between the results of the mathematical modelling and those obtained in real patients. Substantial differences were observed between the two IAP methods (the classic IAP measured at end expiration and the novel MIAP). Based on our findings, we believe that the novel concept of MIAPri may be a better representation for the pressure concealed within the abdominal cavity. Further clinical studies are necessary to reveal the physiological effects of this novel concept.
SA is aveterinary surgeon (DVM, DVSc) and a medical research consultant in laboratory animal researches in the field of trauma, haemorrhage, critical care, and anaesthesia. MLNGM is a former president and treasurer of the World Society of the Abdominal Compartment Syndrome and is the ICU and High Care Burn Unit Director of the Department of Intensive Care in Ziekenhuis Netwerk Antwerpen Stuivenberg.
See additional file 1.
abdominal compartment syndrome
- C ab :
- IAPee :
- IAPei :
mean intra-abdominal pressure (geometrical mean)
- MIAPri :
respiratory-integrated mean intra-abdominal pressure
- P alv :
- P mean :
mean airway pressure
- P plat :
plateau airway pressure
positive end-expiratory pressure
thoraco-abdominal index of transmission
World Society of the Abdominal Compartment Syndrome.
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Ahmadi-Noorbakhsh S, Malbrain MLNG: Addendum: Mathematical model for calculation of mean intra-abdominal pressure, taking into account integration of inspiratory and expiratory intra-abdominal pressure. Ann Intensive Care 2012. Supplement 2 (in press)
This article has been published as part of Annals of Intensive Care Volume 2 Supplement 1, 2012: Diagnosis and management of intra-abdominal hypertension and abdominal compartment syndrome. The full contents of the supplement are available online at http://www.annalsofintensivecare.com/supplements/2/S1.
MLNGM is a member of the medical advisory board of Pulsion Medical Systems, Munich, Germany.
SA and MLNGM planned the study and were responsible for the design, coordination, and drafting the manuscript. SA developed the mathematical model for MIAP calculation and performed the theoretical analyses. MLNGM performed the data collection and statistical analysis for the human pilot study. Both authors read and approved the final manuscript.
Electronic supplementary material
Additional file 1: Mathematical model for calculation of mean intra-abdominal pressure, taking into account integration of inspiratory and expiratory intra-abdominal pressure. (DOCX 35 KB)
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Ahmadi-Noorbakhsh, S., Malbrain, M.L. Integration of inspiratory and expiratory intra-abdominal pressure: a novel concept looking at mean intra-abdominal pressure. Ann. Intensive Care 2 (Suppl 1), S18 (2012). https://doi.org/10.1186/2110-5820-2-S1-S18
- Tidal Volume
- Abdominal Compartment Syndrome
- Peep Level
- Dynamic Compliance
- Pulsion Medical System