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Year : 2020  |  Volume : 20  |  Issue : 3  |  Page : 97-104

Global longitudinal strain changes during hemorrhagic shock: An experimental study

1 Department of Anesthesiology and Intensive Care, North Hospital, APHM, Aix Marseille Univ., INSERM, INRA, C2VN, Marseille, France
2 Department of Anesthesiology, Critical Care, Montpellier University, Pain and Emergency Medicine, Nîmes University Hospital; Faculty of Medicine, Montpellier-Nimes University,EA 2992, Nîmes, France
3 Department of Sports Medicine and Cardiology (CEMAPS 30), Nîmes University Hospital and PhyMedExp, INSERM U1046, CNRS UMR9214, Montpellier University, Montpellier, France

Date of Submission29-Feb-2020
Date of Decision04-May-2020
Date of Acceptance19-May-2020
Date of Web Publication18-Jul-2020

Correspondence Address:
Dr. Xavier Bobbia
Department of Anesthesiology, Critical Care, Pain and Emergency Medicine, Nîmes University Hospital, Place du Pr. Robert Debré, 30029 Nîmes
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Source of Support: None, Conflict of Interest: None

DOI: 10.4103/2452-2473.290066

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OBJECTIVES: Global longitudinal strain (GLS) appears sensitive and reproducible to identify left ventricular systolic dysfunction. The main objective was to analyze the GLS changes in an anesthetized-piglet model of controlled hemorrhagic shock (HS). The secondary objective was to evaluate if GLS changes was different depending on the expansion fluid treatment with or without norepinephrine.
METHODS: Eighteen anesthetized and ventilated piglets were bled until the mean arterial pressure reached 40 mmHg. Controlled hemorrhage was maintained for 30 min before randomizing the piglets to three resuscitation groups: control group, LR group (resuscitated with lactated ringer), and NA group (resuscitated with lactated ringer and norepinephrine).
RESULTS: There was no difference in the baseline hemodynamic, biological, and ultrasound data among the three groups. During the hemorrhagic phase, the GLS increased significantly from 25 mL/kg of depletion. During the resuscitation phase, the GLS decreased significantly from 20 mL/kg of fluid administration. There was no difference in GLS variation among the groups during the hemorrhagic, maintenance, and resuscitation phases.
CONCLUSION: In our HS model, GLS increased with hemorrhage and decreased during resuscitation, showing its preload dependence.

Keywords: Hypovolemia, strain, systolic function

How to cite this article:
Zieleskiewicz L, Claret PG, Muller L, La Coussaye JE, Lefrant JY, Schuster I, Roger C, Bobbia X. Global longitudinal strain changes during hemorrhagic shock: An experimental study. Turk J Emerg Med 2020;20:97-104

How to cite this URL:
Zieleskiewicz L, Claret PG, Muller L, La Coussaye JE, Lefrant JY, Schuster I, Roger C, Bobbia X. Global longitudinal strain changes during hemorrhagic shock: An experimental study. Turk J Emerg Med [serial online] 2020 [cited 2023 May 30];20:97-104. Available from: https://www.turkjemergmed.org/text.asp?2020/20/3/97/290066

  Introduction Top

Conventional techniques for determining systolic function are based on volume changes or visual assessment of wall motions; strain echocardiography measures tissue deformation within the myocardium.[1] The acquisition method used by strain to derive global longitudinal strain (GLS) appears more sensitive and more reproducible than left ventricular (LV) ejection fraction to identify LV systolic dysfunction.[2] In addition, some studies have suggested that GLS may become a major parameter for the detection and prognostic assessment of patients with diastolic dysfunction.[3] GLS is feasible in emergency patients and some authors believe that it should be considered for inclusion in the Emergency Ultrasound Fellowship curriculum.[4] Given the formula for calculating the GLS, it could vary according to the blood volume. The use of GLS in acute patients to assess cardiac function is therefore in full development and we wonder if its values are not dependent on blood volume.

Hemorrhagic shock (HS) reduces tissue perfusion and oxygen delivery, leading to cellular dysfunction and multiple organ failure.[5] The first line of HS treatment is to restore circulatory stability with rapid fluid administration and many studies suggest that vasopressors may be beneficial to treat.[6],[7] In the presence of life-threatening hypotension, administration of vasopressors, particularly norepinephrine (NE), is recommended in addition to fluids to maintain target arterial pressure.[8]

The main objective of this study was to analyze the GLS changes in an anesthetized-piglet model of near-fatal controlled hemorrhage. The secondary objective was to evaluate if GLS changes were different depending on the expansion fluid treatment with or without NE.

  Methods Top


This study was designed as a prospective, randomized, unblinded trial in a piglet model. The Animal Care and Use Committee of Languedoc-Roussillon (CEEA-LR-12013) approved the protocol and all experiments were performed in an authorized animal research laboratory. This animal study was conducted according to the European Directive 2010/63/EC regulating the use of animals in science. All facilities and transport comply with current legal requirements. Our hypothesis was that GLS values were dependent on blood volume. Thus, in a HS model, GLS would increase with hemorrhage and decrease with fluid loading.

Animal preparation

Eighteen piglets of about 30 kg were included. The piglets used were large, white females, about 2½ months old. Animals were fasted overnight with free access to water. The piglets were premedicated by i.m. injection of ketamine 10 mg/kg, atropine 0.05 mg/kg, and midazolam 1 mg/kg. Anesthesia was induced with a bolus dose of propofol (4 mg/kg) and cisatracurium (0.25 mg/kg) via an ear vein. Anesthesia was maintained with propofol (8 mg/kg/h) and neuromuscular block was achieved with cisatracurium (0.5 mg/kg/h). After surgical tracheostomy (6.5 tracheal tube Tyco®, Atlanta, GA, USA), animals' lungs were ventilated with an inspired fraction of oxygen of 0.21, a tidal volume of 8 mL/kg, and a positive end-expiratory pressure of 5 cm H2O.

Once the piglets were anesthetized, a 7 French double-lumen catheter was inserted with ultrasound guidance through the internal jugular vein into the right atrium. The central venous line was used to monitor central venous pressure and to inject cold boluses for transpulmonary thermodilution. A 5 French arterial catheter with an integrated thermistor tip was inserted through the femoral artery (PiCCO® Plus; Pulsion Medical Systems, Munich, Germany) and into the descending aorta for continuous arterial pressure monitoring, arterial blood sampling, and cardiac output (CO) transpulmonary thermodilution measurement. Stroke volume (SV) was calculated as follows: CO (by thermodilution)/heart rate (HR). The femoral vein was also cannulated with an 8.5 French catheter (Arrow®; Arrow International, Inc., Cleveland, OH, USA) for blood withdrawal and for the administration of resuscitation fluids. All pressure-measuring catheters were connected to transducers (PiCCO® Plus) for continuous recording of systemic arterial pressure, HR, and temperature.

Experimental protocol and measurement times

The study design shown in [Figure 1] has already been published:[9],[10] T0 was the start of the experiment; the measured mean arterial pressure (MAP) was considered the reference MAP. T1 was reached when MAP reached 40 mmHg. MAP was maintained for 30 min at 35–45 mmHg (T2). The hemorrhage ended after T2. Fluids could be administered or the bleeding could be continued for this objective. The piglet was then resuscitated until a MAP equal to its baseline MAP was reached. Finally, MAP was maintained at ±10% of the reference MAP for 1 h. Eighteen piglets were randomly allocated by sealed envelopes into three groups based on the type of resuscitation. Until T2[Figure 1], the procedure was the same for the three groups. The control group (n = 6) was just monitored and neither treatment was administrated. As there was no resuscitation phase in this group, the T3 time did not exist and the T4 time after 1 h of MAP was between 35 and 45 mmHg. The LR group (n = 6) was resuscitated with lactated ringer's (LR) solution and the third group received LR and norepinephrine administration (NA; n = 6). NE was infused with a stable infusion rate of 0.5 μg/kg/min. Measurements were performed at every 5 mL/kg of bleeding during the hemorrhagic phase (T0a, T0b, etc.) and every 10 mL/kg of fluid infusion during the resuscitation phase (T2a, T2b, etc.). For the LR and NA groups, MAP was maintained at its baseline value ±10% by additional fluid infusion according to the allocated group for a further hour; then, all animals were killed using i. v. thiopental infusion (2 g). Hemodynamic parameters were transcribed from the PiCCO® monitor. CO was measured by transpulmonary thermodilution, extravascular lung water, and pulse pressure variation (PPV) by pulse contour analysis. Blood biochemistry values were analyzed at all times (T0–T4): arterial lactate, arterial pH, hemoglobin, plasma HCO3, and plasma creatinine.
Figure 1: Study design. MAP: Mean arterial pressure

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Conventional echocardiography

Images were obtained with a Vivid S70 ultrasound device (Vivid S70, GE Medical Systems, Milwaukee, WI, USA) equipped with a phased-array transducer (M5S). Velocity time integral of the subaortic blood flow (VTI) was computed on an apical five-chamber view using pulse Doppler in the left ventricle outflow chamber. The apical view was used to attain tissue Doppler across the mitral annulus. Pulse tissue Doppler imaging velocities were acquired at the lateral mitral annuli and included the peak systolic (s') velocity.

Strain echocardiography

Strain echocardiography measures actual tissue deformation within the myocardium. The definition of strain (ε) is “the relative change in length of a material related to its original length.”[1] The strain calculation is based on the distance between two points in systole (Lsyst) and in diastole (Ldiast): (ε = (Lsyst– Ldiast)/Ldiast).[1],[11]

Strain is a dimensionless measurement of deformation, expressed as a percentage change from an object's original dimension. In the present study, we measured only longitudinal strain because, in general, longitudinal LV mechanics, which are predominantly governed by the subendocardial region, are the most vulnerable component of LV mechanics and, therefore, are most sensitive to the presence of myocardial disease. We acquired two-dimensional gray-scale in the apical four-chamber for one cardiac cycle and stored the results digitally for subsequent off-line analysis using commercially available automated function imaging (AFI) software (EchoPAC Workstation, BT09, GE-VingMed, Horten, Norway). The peak systolic longitudinal strain was obtained from the apical four-chamber view using the AFI software, and the mean peak systolic longitudinal strain obtained from the standard apical four-chamber view was considered the global peak systolic longitudinal strain (GLS).

Statistical analysis

As no study had investigated the GLS changes in HS, no calculation of sample size was possible. Quantitative data were expressed as median with 25th and 75th percentiles (25th percentile–75th percentile). Qualitative variables were expressed as frequency with percentages. Comparison of quantitative variables among the different groups was performed by a nonparametric test (Mann–Whitney U-test or Kruskal–Wallis test if multiple classes were used). The relationship between two variables was tested by the Chi-square test or by the Fisher's exact test when Chi-square conditions of application (theoretical numbers <5) were not met. Correlation coefficients were calculated to assess the relationship between GLS and PPV. The significance level was set at 5% for all tests. Statistical analysis was performed under R 3.3.3 (2017, R Foundation for Statistical Computing, Vienna, Austria).

  Results Top

Animals and compliance with protocol

Eighteen piglets were randomly allocated to the control, LR, or NA group (six per group). All phases of the experiment were respected for all piglets.


On all piglets, 215 GLS measures were attempted and 178 were successful (83%). The success rates were, respectively, for T0, T0a, T0b, T0c, T0d, T0e, T1, T1a, T2, T2a, T2b, T2c, T3, T3a, and T4 as follows: 100%, 94%, 82%, 100%, 92%, 80%, 65%, 72%, 65%, 88%, 100%, 100%, 100%, 75%, and 74%. Weight, mean hemodynamic, and ultrasound data at the beginning (T0) of the study and during T1, T2, T3, and T4 times are shown in [Table 1]. [Table 2] shows necessary volumes for induced, maintained HS and for resuscitation and stabilization. The mean biological data at all times of measurements are given in [Table 3].
Table 1: Hemodynamic and ultrasound data at baseline (T0), during hemorrhagic shock (T1, T2), and after fluid resuscitation (T3, T4) in the control, lactated ringer, and norepinephrine administration groups

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Table 2: Volumes of hemorrhage and resuscitation fluid (mL/kg) in the control, lactated ringer, and norepinephrine administration groups

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Table 3: Biological data at baseline (T0), during hemorrhagic shock (T2), and after fluid resuscitation (T3, T4) in the control, lactated ringer , and norepinephrine administration groups

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GLS changes during the experiment for all groups are shown in [Figure 2]. Comparison between GLS and SV changes during hemorrhagic and maintenance phases is shown in [Figure 3]. The correlation coefficient between GLS and PPV was 0.27 (IC 95% [0.11; 0.41]; P < 0.01). [Figure 4] shows the comparisons of GLS changes and PPV.
Figure 2: GLS changes for all groups. (a) GLS changes for all groups; (b) changes for each group; dark gray boxplots: control group; white boxplots: LR group; light gray boxplots: NA group; dashed square brackets: P > 0.05; solid lines square brackets: P < 0.05; GLS: Global longitudinal strain

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Figure 3: GLS and SV changes. (a) GLS and SV values in hemorrhagic and maintenance phase; (b) GLS and SV changes between all step in hemorrhagic and maintenance phase; white boxplots: GLS; gray boxplots: SV; dashed square brackets: P > 0.05; solid lines square brackets: P < 0.05; SV: Stroke volume; GLS: Global longitudinal strain

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Figure 4: GLS and PPV changes. (a) GLS and PPV values; (b) GLS and PPV changes between all steps; white boxplots: GLS; gray boxplots: PPV; dashed square brackets: P > 0.05; solid lines square brackets: P < 0.05; GLS: Global longitudinal strain; PPV: Pulse pressure variation

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  Discussion Top

Main results

Our study shows that in a HS piglet model, GLS increases during hemorrhage and decreases during resuscitation. However, after 10 at 20 mL/kg of hemorrhage, GLS changes seem faster than SV and PPV.

This study describes for the first time the course of myocardial strain during hemorrhage. As a primary result, GLS is closely related to blood volume variation as it increases in response to blood removal and decreases during blood volume compensation. Due to its first use in the cardiology setting, only a few studies have investigated the influence of preload on GLS. In patients with a low preload dependency, GLS was first described as independent of the preload.[12] However, animal and human studies have underlined the influence of preload on GLS in hypovolemic subjects.[13],[14],[15] This discrepancy between hypovolemic and nonhypovolemic patients can be explained by the formula of GLS (Lsyst– Ldiast)/Ldiast. Indeed, in all the patients, whatever their hemodynamical status, Ldiast will be mechanically affected by loading or unloading (end diastolic stretch of the myocardial fibers). Conversely, due to their position in the Franck-Starling curve, Lsyst will be affected in preload-dependent patients only (preload induced changes in inotropism).[15] Consequently, the variations of GLS due to the changes in preload will be amplified in hypovolemic patients. Hence, we tested both GLS and PPV at all stages of the experiment. Interestingly, we confirmed for the first time that PPV and GLS were correlated. In 2014, Cameli et al. emphasized the ability of atrial longitudinal strain to predict a PPV >15% in mechanically ventilated patients.[16] Nevertheless, the left atrial longitudinal strain reflects filing pressure (i.e., a static index) and probably less accurate than ventricular GLS variations for the prediction of fluid responsiveness. Future studies evaluating the ability of GLS variations after a change in preload to predict fluid responsiveness are, therefore, necessary. In clinical practice, interpretation of GLS values to assess cardiac function should be relevant only in patients with controlled blood volume.

NE is the recommended amine in HS states.[8] Some animal studies have shown the positive effect of NE on myocardial performance.[17],[18] In our study, no significant difference was found between the LR and NA groups during the resuscitation phase for GLS changes.

We cannot know from this model if GLS is able to detect myocardial dysfunction in HS. It is likely that in our HS model, the shock state does not last long enough to induce significant myocardial dysfunction. However, the GLS aggravation after 10 at 20 mL/kg of depletion is more important than SV and PPV. Probably, the GLS does not vary only according to the preload in this model. These results will have to be completed in order to understand their meaning.


First, the findings of the present study may not be extrapolated to trauma patients as no direct tissue damage was induced in this model. Second, NE was infused with a stable infusion rate of 0.5 μg/kg/min, which differs from usual clinical practice. Third, baseline arterial blood lactate appears to be lower in the LR group; we have no explanation and we do not think it influences the results. In addition, the use of a MAP-based HS modality results in a variation in the volume of hemorrhage to induce shock and the volume of infusion for resuscitation. Finally, GLS was evaluated by only a four-chamber view. However, there is a good correlation between GLS and the 4-chamber view strain values.[15]

  Conclusion Top

In this controlled HS model, GLS increased linearly with hemorrhage and decreased during resuscitation. These results confirm a preload dependency of GLS. During hemorrhage, GLS variations should not be interpreted as a variation of systolic function but rather as a consequence of hypovolemia.


The authors acknowledge Marylene Peltier for her help in administrative, technical, and logistical support, Nadege Magnan for her help in administrative support, and Marc Giet and Jack Fountain for the preparation of the animals and for their technical assistance.


None declared.

Author contributions statement

TM, LZ, LM, CR, and XB conceived and designed the experiments; TM, CR, and XB performed the experiments; TM, LZ, PGC, LM, and XB analyzed and interpreted the data; TM and XB contributed reagents, materials, analysis tools, or data; TM, LZ, PGC, JELC, LM, JYL, CR, and XB wrote the paper.

Conflicts of interest

XB declares a competing interest as a US teacher for GE (GE MEDICAL SYSTEMS ULTRASOUND) customers. The other authors state they have no competing interests.

Ethical Approval

The Animal Care and Use Committee of Languedoc-Roussillon (CEEA-LR-12013) approved the protocol and all experiments were performed in an authorized animal research laboratory. This animal study was conducted according to the European Directive 2010/63/EC regulating the use of animals in science.

  References Top

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Nesbitt GC, Mankad S, Oh JK. Strain imaging in echocardiography: Methods and clinical applications. Int J Cardiovasc Imaging 2009;25 Suppl 1:9-22.  Back to cited text no. 2
Haugaa KH, Edvardsen T. Global longitudinal strain: The best biomarker for predicting prognosis in heart failure? Eur J Heart Fail 2016;18:1340-1.  Back to cited text no. 3
Reardon L, Scheels WJ, Singer AJ, Reardon RF. Feasibility and accuracy of speckle tracking echocardiography in emergency department patients. Am J Emerg Med 2018;36:2254-9.  Back to cited text no. 4
Ao-Ieong ES, Williams A, Jani V, Cabrales P. Cardiac function during resuscitation from hemorrhagic shock with polymerized bovine hemoglobin-based oxygen therapeutic. Artif Cells Nanomed Biotechnol 2017;45:686-93.  Back to cited text no. 5
Stadlbauer KH, Wagner-Berger HG, Raedler C, Voelckel WG, Wenzel V, Krismer AC, et al. Vasopressin, but not fluid resuscitation, enhances survival in a liver trauma model with uncontrolled and otherwise lethal hemorrhagic shock in pigs. Anesthesiology 2003;98:699-704.  Back to cited text no. 6
Stadlbauer KH, Wenzel V, Wagner-Berger HG, Krismer AC, Königsrainer A, Voelckel WG, et al. An observational study of vasopressin infusion during uncontrolled haemorrhagic shock in a porcine trauma model: Effects on bowel function. Resuscitation 2007;72:145-8.  Back to cited text no. 7
Rossaint R, Bouillon B, Cerny V, Coats TJ, Duranteau J, Fernández-Mondéjar E, et al. The European guideline on management of major bleeding and coagulopathy following trauma: Fourth edition. Crit Care 2016;20:100.  Back to cited text no. 8
Roger C, Muller L, Deras P, Louart G, Nouvellon E, Molinari N, et al. Does the type of fluid affect rapidity of shock reversal in an anaesthetized-piglet model of near-fatal controlled haemorrhage? A randomized study. Br J Anaesth 2014;112:1015-23.  Back to cited text no. 9
Roger C, Louart B, Louart G, Bobbia X, Claret PG, Perez-Martin A, et al. Does the infusion rate of fluid affect rapidity of mean arterial pressure restoration during controlled hemorrhage. Am J Emerg Med 2016;34:1743-9.  Back to cited text no. 10
D'hooge J, Heimdal A, Jamal F, Kukulski T, Bijnens B, Rademakers F, et al. Regional strain and strain rate measurements by cardiac ultrasound: Principles, implementation and limitations. Eur J Echocardiogr 2000;1:154-70.  Back to cited text no. 11
Mendes L, Ribeiras R, Adragão T, Lima S, Horta E, Reis C, et al. Load-independent parameters of diastolic and systolic function by speckle tracking and tissue Doppler in hemodialysis patients. Rev Port Cardiol 2008;27:1011-25.  Back to cited text no. 12
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  [Figure 1], [Figure 2], [Figure 3], [Figure 4]

  [Table 1], [Table 2], [Table 3]

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