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Stretchactivated current in human atrial myocytes and Na^{+} current and mechanogated channels’ current in myofibroblasts alter myocyte mechanical behavior: a computational study
BioMedical Engineering OnLine volume 18, Article number: 104 (2019)
Abstract
Background
The activation of stretchactivated channels (SACs) in cardiac myocytes, which changes the phases of action potential repolarization, is proven to be highly efficient for the conversion of atrial fibrillation. The expression of Na^{+} current in myofibroblasts (Mfbs) regenerates myocytes’ action potentials, suggesting that Mfbs play an active role in triggering cardiac rhythm disturbances. Moreover, the excitation of mechanogated channels (MGCs) in Mfbs depolarizes their membrane potential and contributes to the increased risk of postinfarct arrhythmia. Although these electrophysiological mechanisms have been largely known, the roles of these currents in cardiac mechanics are still debated. In this study, we aimed to investigate the mechanical influence of these currents via mathematical modeling. A novel mathematical model was developed by integrating models of human atrial myocyte (including the stretchactivated current, Ca^{2+}–force relation, and mechanical behavior of a single segment) and Mfb (including our formulation of Na^{+} current and mechanogated channels’ current). The effects of the changes in basic cycle length, number of coupled Mfbs and intercellular coupling conductance on myocyte mechanical properties were compared.
Results
Our results indicated that these three currents significantly regulated myocyte mechanical parameters. In isosarcometric contraction, these currents increased segment force by 13.8–36.6% and dropped element length by 12.1–31.5%. In isotonic contraction, there are 2.7–5.9% growth and 0.9–24% reduction. Effects of these currents on the extremum of myocyte mechanical parameters become more significant with the increase of basic cycle length, number of coupled Mfbs and intercellular coupling conductance.
Conclusions
The results demonstrated that stretchactivated current in myocytes and Na^{+} current and mechanogated channels’ current in Mfbs significantly influenced myocyte mechanical behavior and should be considered in future cardiac mechanical mathematical modeling.
Background
As an alternative of experimental studies, computational modeling studies provide a powerful framework for gaining substantial insights of cardiac electrophysiology and mechanics in many aspects [1, 2]. For cardiac electrophysiological simulation, cardiac cell action potential (AP) models are built to represent current flow through ion pumps, channels, and exchangers [3, 4]. For mechanical simulation, the active stress/strain models and Hill’s threeelement model have been formulated to lay out active contraction [5, 6].
Cardiac electrical activities have intimate connection with mechanical actions. The interaction between them is referred as electromechanical coupling (EMC) and mechanoelectrical feedback (MEF) [7]. As a major mechanism of the MEF, the stretchactivated channel (SAC) has been used to explain changes in electrophysiological behavior by mechanical deformation. Several cellular experimental and modeling studies have examined the impact of SACs on cardiac electrophysiology [8,9,10,11].
Recently, clinical data and simulation studies have provided some important insights into cardiac structural remodeling, especially fibrosis as a hallmark of permanent atrial fibrillation. Many of them verified that both fibroblasts and myofibroblasts (Mfbs) modulated cardiac electrical conduction, coordinated tissue remodeling, and integrated signals [12,13,14]. They have been considered as active communicators rather than nonexcitable cells, which involve several currents like cardiac myocytes, e.g., the currents through potassium channels [15, 16], the nonselective transient receptor potential cationic channel subfamily M member 7 (TRPM7) [17], voltagegated sodium channels (VGSCs) [18, 19], chloride channels [20], single mechanogated channels (MGCs) [21], and voltagedependent proton currents [22].
Computational models of atrial fibrosis have been used to investigate how fibroblasts modulate cardiac myocyte electrophysiology. At the cellular level, processes of fibrotic remodeling are represented as fibroblast proliferation and phenotype switching [23, 24]. Simulation results showed that coupling of fibroblasts or Mfbs to atrial myocytes resulted in shorter duration of the action potential (APD), slower conduction, and spiral wave breakups [25,26,27,28].
As a critical determinant of cardiac mechanics, fibroblastmediated changes in extracellular matrix structure are also investigated by computational modeling. Cell compaction of collagen gels has been studied by explicitly calculating the mechanical equilibrium between each cell’s contractile forces and nearby collagen fibers’ mechanical properties [29, 30]. Infarct mechanics has been simulated by coupling agentbased model predictions to a finite element model [31, 32]. These studies have found that fibroblast alignment parallel to a strain cue provides a negative feedback to radical changes in local fiber orientations.
Previous studies mentioned above have examined cardiac myocyte functions in many aspects; however, no study to the our best knowledge has considered the following two aspects in Mfb–myocyte (Mfb–M) coupling, especially in EMC: (1) the stretchactivated ion channel current (I_{SAC}) in myocytes, which influences cardiac myocytes electrophysiological characteristics under stretching [33, 34]; (2) the currents through VGSCs (I_{Na_Mfb}) and MGCs (I_{MGC_Mfb}) in Mfbs, which could influence Mfb properties and contribute to EMC in cardiac pathologies [18, 21].
Our previous study has found that I_{Na_myofb} and I_{MGC_Mfb} regenerated APs in myocytes and Mfbs [28]. In this study, we aimed to investigate the role of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} in the mechanical contraction of cardiac myocyte. Simulation results of human atrial myocyte segment mechanical dynamics with different gapjunctional conductance (G_{gap}), number of coupled Mfbs and basic cycle lengths (BCLs) were examined.
Results
Effects of I _{SAC}, I _{Na_Mfb}, and I _{MGC_Mfb} on atrial myocyte AP, [Ca^{2+}]_{i}, and the normalized force
Figure 1 shows the combinational effects in five groups (see “Simulation protocol” section) of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} on the membrane potential, intracellular Ca^{2+} concentration and the normalized force (F_{norm}) of myocytes with a G_{gap} of 3 nS and a BCL of 1 s. For myocytes, coupling Mfbs (Group 25) resulted in gradual decrease of myocyte membrane potential amplitude (V_{max}) and APD at 90% repolarization (APD_{90}), and increase of the resting myocyte membrane potential (V_{rest}) depolarization (Fig. 1a). Meanwhile, a spontaneous excitement was emerged in Group 5, in which the peak [Ca^{2+}]_{i} dropped significantly (Fig. 1b), indicating that I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} could result in discordant alternans. From the traces of F_{norm} (Fig. 1c), it can be observed that the peak F_{norm} increased after myocyte coupled to Mfbs. It was increased by 7.6% (Group 2), 14.5% (Group 3), 38.7% (Group 4), and 19.2% (Group 5) as compared to the control (Group 1). It was remarkable that Group 4 got the biggest F_{norm} increment, which meant F_{norm} of myocytes could be significantly enhanced by the combination of I_{SAC} and I_{Na_Mfb}. However, the increment relatively declined in Group 5 with the introduction of I_{MGC_Mfb}. This might suggest that deformation in myocytes enhanced F_{norm}, while in Mfbs the deformation relatively hindered it. The effects of I_{SAC} and I_{MGC_Mfb} on the force of atrial myocytes were opposite, with I_{SAC} increasing and the other one decreasing.
Effects of I _{SAC}, I _{Na_Mfb}, and I _{MGC_Mfb} on atrial myocyte segment mechanical parameters
Traces of F_{SE}, F_{PE}, F_{segment}, l_{CE}, l_{PE}, and l_{SE} obtained in five groups for the simulations of isosarcometric contraction with sarcomere length of 1.78 µm are displayed in Fig. 2, and the ones for simulations of isotonic contraction with applied force of 10 mN per square millimeter (mN/mm^{2}) are displayed in Fig. 3.
In isosarcometric contraction (Fig. 2), F_{PE} and l_{PE} in five groups were constant. Peak F_{SE} increased when myocyte coupled to Mfbs. It was increased by 7.2% (Group 2), 13.8% (Group 3), 36.6% (Group 4), and 18.5% (Group 5) as compared to the control (Group 1). Using Eq. (14) (see “Mechanical behavior of a single segment” section), the increments in F_{segment} were the same as those in F_{SE}. On the contrary, l_{CE} decreased when myocyte coupled to Mfbs. The minimum of l_{CE} was dropped by 6.4% (Group 2), 12.1% (Group 3), 31.5% (Group 4), and 16.2% (Group 5) as compared to the control (Group 1). Using Eq. (15), the changes in l_{CE} were equal to those in l_{SE}. Similar to Fig. 1, Group 4 had the most significant change, indicating that the combination of I_{SAC} and I_{Na_Mfb} played a significant role in determining myocyte segment mechanical behavior.
In isotonic contraction (Fig. 3), F_{segment} in five groups was constant. Like Fig. 2a, the peak value of F_{SE} also increased when Mfbs were coupled. It was increased by 1.6% (Group 2), 2.7% (Group 3), 5.9% (Group 4), and 2.5% (Group 5) as compared to the control (Group 1). The increments were smaller than those in isosarcometric contraction. According to Eq. (14), the decrements in F_{PE} were equal to the increments in F_{SE}. The minimum of l_{CE} was dropped by 4.3% (Group 2), 7.4% (Group 3), 15.8% (Group 4), and 6.3% (Group 5) as compared to the control (Group 1), while the peak value of l_{SE} was increased by 0.6%, 1.4%, 3.7%, and 0.9%, and finally, l_{PE} were declined by 6.8%, 11.4%, 24.0%, and 10.0%. I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} not only changed the extreme values of l_{CE}, l_{PE}, and l_{SE}, but also altered l_{CE} and l_{SE} in the resting stage. For example, the value of l_{SE} in resting period was 0.0021 μm (Group 1), 0.0013 μm (Group 2), 0.0021 μm (Group 3), 0.0051 μm (Group 4), and 0.0032 μm (Group 5), respectively. Similarly, Group 4 has the most impact on the mechanical parameters.
To investigate the effects of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} on the extreme values of atrial myocyte segment mechanical parameters, we simulated five groups with different BCLs, Mfb–M ratios, and G_{gap} in both isosarcometric contraction (Fig. 4) and isotonic contraction (Fig. 5).
From the traces of the extremum of F_{SE}, F_{segment}, l_{CE}, and l_{SE} for BCL = 0.1–2 s (Fig. 4a–d), it could be observed that peak F_{SE} (F_{SE[MAX]}), peak F_{segment} (F_{segment[MAX]}), and peak l_{SE} (l_{SE[MAX]}) increased, and valley value of l_{CE}(l_{CE[MIN]}) decreased with increasing BCL, in isosarcometric contraction. When BCL was less than 1 s, F_{SE[MAX]}, F_{segment[MAX]} and l_{SE[MAX]} at each BCL increased and l_{CE[MIN]} decreased in Groups 2–5 as compared to Group 1. Meanwhile, at each BCL, F_{SE[MAX]}, F_{segment[MAX]}, and l_{SE[MAX]} in Group 4 reached their maximums, and l_{SE[MAX]} obtained its minimum. This suggests that I_{SAC} together with I_{Na_Mfb} had the key influence on myocyte mechanical parameters. The influence disappeared in Group 5, suggesting that the role of I_{MGC_Mfb} in myocytes was opposite compared to I_{SAC}. As BCL longer than 1 s, each parameter in Group 1 to 3 has increased or decreased as a same trend, whereas fluctuated in Group 4 and 5. These phenomena might be attributed to that I_{SAC} and I_{Na_Mfb} enhanced atrial myocytes excitability and triggered spontaneous excitements at large BCLs. [Ca^{2+}]_{i}, the vehicle of EMC, also fluctuated, driving the undulation of mechanical behavior.
Figure 4e–h shows the extremum of four parameters with Mfb–M ratios ranging from 1 to 8. Parameters in Group 1 were constants as no Mfb was coupled to myocytes. Unlike the similar trends of five groups in Fig. 4a–d, the trends of Group 2 and Group 3 in Fig. 4e–h were close and mostly distributed over one side of Group 1, and the trends of Group 4 and Group 5 were similar and distributed over the other side. Our results demonstrated that introducing currents through SACs in myocytes and currents through MGCs in Mfbs in cardiac modeling could lead to different simulation results. In fact, the stretch ability and contractility of myocytes in fibrotic heart were quite different from those in normal heart. Integrated I_{SAC} and I_{MGC_Mfb} in cardiac simulation could help obtain more accurate and closer to experimental results.
Figure 4i–l shows the extremum of four parameters with G_{gap} ranging from 0.5 to 8 nS. Parameters in Group 1 were also constants. The variance of five groups was less than those in other settings (Fig. 4a–h), suggesting the relative small effects of G_{gap} on myocyte mechanical parameters. The traces of Group 2 to 5 were mostly distributed over one side of Group 1. Parameters at each G_{gap} in Group 4 got the highest or lowest value among five groups, and parameters in Group 5 took the second place, indicating that I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} played a strong role in atrial myocyte mechanical behavior.
The extremum of F_{SE}, F_{PE}, l_{CE}, l_{SE}, and l_{PE} as functions of BCL, Mfb–M ratio, and G_{gap} in isotonic contraction are showed in Fig. 5.
In Fig. 5a–e, the parameters among five groups were close to each other. As BCL increased, the values in Group 1, 4 and 5 first increased and then decreased. In these groups, pure myocyte or integrating I_{SAC} and I_{MGC_Mfb} in fibrotic myocyte were more likely to cause discordant alternans and mechanical parameters fluctuation at big BCLs.
In Fig. 5f–j, the parameters in Group 2 always stayed over one side of Group 1 as the coupled ratio increased, while the parameters in other groups finally converged over the other side. It suggested that integrating I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} in fibrotic myocyte significantly influenced the myocyte segment mechanical behavior at large coupled ratios.
In Fig. 5k–o, the parameters in Group 1 were constant, and Group 2, 3, and 5 had the similar traces, while Group 4 got the highest or lowest values. Therefore, I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} had relative influences on mechanical parameters at large G_{gap}.
Discussion
This study investigated the roles of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} in myocyte segment mechanical behavior. To address these issues, computational simulations of the coupled Mfb–M system were performed by employing a combination of models of the human atrial myocyte (including I_{SAC}) and Mfb (including I_{Na_Mfb} and I_{MGC_Mfb}), as well as models of Ca^{2+}–force relation and myocyte mechanical segment. Specifically, effects of these currents with changes in (1) BCL, (2) the number of coupled Mfbs, and (3) G_{gap} on atrial myocyte segment mechanical parameters were investigated. The integration of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} could result in (1) decreased V_{max} and APD_{90}, increased V_{rest} depolarization, and spontaneous excitements even discordant alternans at large BCLs, and (2) increased peak value of F_{SE}, F_{segment}, and l_{SE} and decreased valley value of l_{CE} in isosarcometric contraction, and increased peak value of F_{SE} and l_{SE} and decreased valley value of F_{PE}, l_{CE}, and l_{PE} in isotonic contraction. Moreover, I_{SAC} and I_{MGC_Mfb} have relative effects on myocyte segment mechanical parameters.
Effects of I _{SAC}, I _{Na_Mfb}, and I _{MGC_Mfb} on atrial myocyte segment mechanical properties
Effects of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} on the excitability of human atrial myocytes have been discussed in our previous study [28]. Here, we discussed the roles of these currents in myocyte segment mechanical behavior.
EMC and MEF were two known effects [7], but the physical role of MEF in EMC was still poorly understood. In general, I_{SAC}, handling as the major mechanisms of the MEF, was reported to enhance the early phase of AP repolarization and prolong or delay the final phase of repolarization [9, 35, 36]. But the impact of I_{SAC} on cardiac mechanics, to our best knowledge, has been rarely studied so far. In our present study, the stretchactivated currents had the most significant influence on myocyte segment mechanical parameters in both isosarcometric contraction and isotonic contraction.
For cardiac Mfbs, many studies have verified that mechanical cues activated cardiac Mfbs and led to increased production of extracellular matrix [37, 38]. Mfbs were regarded as a critical determinant of cardiac mechanics. Previous studies have used computational modeling to demonstrate the acute mechanical effects on cardiac fibroblast structure and organization [39, 40]. They found that an axial strain environment could guide fibroblast proliferation, orientation, and migration [31, 41, 42]. Several groups have simulated cell compaction of collagen gels by calculating mechanical equilibrium between each cell’s contractile forces and nearby collagen fibers’ mechanical properties. They reported that cellular organization is tightly linked to the mechanical feedback loop between cells and matrix [29, 30]. These studies were all about the stretchinduced responses of quiescent cardiac Mfbs. However, the inverse process, i.e., the Mfbsinduced responses of cardiac mechanics, has not been widely explored. Our results showed that coupling Mfbs changed myocytes mechanical properties. In addition, we compared the results of before and after adding I_{Na_Mfb} and I_{MGC_Mfb} in the Mfb model, and found that the effects of I_{MGC_Mfb} on the force of atrial myocytes were contrary to I_{SAC}.
For I_{Na_Mfb}, many studies have been conducted to investigate how this current could influence Mfb proliferation [18, 43]. Our results showed that I_{Na_Mfb} decreased V_{max} and APD_{90} and increased V_{rest} depolarization in myocytes. This depolarization changed diastolic Ca^{2+} levels and then altered myocytes mechanical behavior.
For I_{MGC_Mfb}, experimental data have indicated that cardiac fibroblasts expressed functional MCGs, contributing to the cardiac MEF both under physiological and pathophysiological conditions [44, 45]. We assumed that it could affect myocytes mechanical characteristics like I_{SAC}. Our results supported this hypothesis. In our simulations, I_{MGC_Mfb} altered myocytes mechanical behavior. Interestingly, the effects of I_{MGC_Mfb} and I_{SAC} on myocyte segment mechanical parameters seemed to be opposite. Myocytes stretch activated I_{SAC} and enhanced the influence on mechanical parameters, while Mfbs compression activated I_{MGC_Mfb} and weakened the influence. Moreover, MGCs were activated by fibroblast compression and inactivated by fibroblast stretch [21], implying that I_{MGC_Mfb} should be integrated in cell modeling only during cell compression, such as fibroblasts/Mfbs compression caused by stretching and dilatation of surrounding cardiac myocytes.
Mfb was a critical determinant of cardiac mechanics. Previous studies have demonstrated that abnormal quantity or organization of Mfb could lead to both systolic and diastolic dysfunction [12, 30, 46]. Besides, previous modeling work suggested that Mfb–M coupling contributed to arrhythmia formation [25, 47]. The key factors included BCL, the number of coupled Mfbs, and G_{gap}. Here, we integrated I_{Na_Mfb}, I_{SAC}, and I_{MGC_Mfb} into Mfb–M coupling and compared their effects on myocyte mechanical properties in different settings of BCL, Mfb–M ratio, and G_{gap}. To the best of our knowledge, this has not been examined before. With BCL, Mfb–M ratio, and G_{gap} increasing, impacts of these currents on the extremum of myocyte mechanical parameters became greater, as summarized in Figs. 4 and 5.
Limitations
Two limitations in the present study should be mentioned. First, functional roles of SACs in Mfbs were not considered. Direct proof of mechanoactivation of mechanosensitive channels in cardiac Mfbs was limited. A handful of experimental studies have found that mechanical cues could lead to the opening of socalled SACs, and transient receptor potential canonical channels were candidates for the stretchactivated currents measured in cardiac fibroblasts [48, 49]. However, the current–voltage relation of I_{SAC} in Mfbs needs further study. Second, the breadth of this computational study needs to be extended. Our work focused on the scale of local cell–cell interactions. Other scales, such as scales of subcellular signaling, cell–matrix interactions, tissue remodeling, and organ level conduction properties, were not included in this preliminary study. In fact, processes across these scales did not occur in isolation but operated as an interconnected system with every level passing information to other levels. Therefore, multiscale modeling frameworks still need to be developed, although they brought computational challenges, and such models involving cardiac Mfbs and fibrosis were still rare.
Conclusions
This study demonstrated the combinational effects of I_{SAC} in myocytes and I_{Na_Mfb} and I_{MGC_Mfb} in Mfbs on myocyte mechanical properties. Our results showed that the addition of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} regulated the peak and valley values of myocyte mechanical parameters in both isosarcometric contraction and isotonic contraction. Effects of these currents on the extremum of myocyte mechanical parameters become more evident as BCL, Mfb–M ratio, and G_{gap} increased. The effects proved that the stretchactivated current in atrial myocyte and Na^{+} current and mechanogated channels in Mfbs should be considered in future pathological cardiac mechanical mathematical modeling, such as atrial fibrillation and cardiac fibrosis.
Methods
Mathematical model was developed by integrating (1) the model of the human atrial myocyte [50], (2) the model of I_{SAC} [33], (3) the model of Ca^{2+}–force relation [51, 52], (4) the active model of the human cardiac Mfb [26], (5) our proposed formulation of I_{Na_Mfb} and I_{MGC_Mfb} based on experimental findings from Chatelier et al. [18] and Kamkin et al. [21], and (6) the Hill threeelement rheological scheme of a single segment of myocyte [53, 54]. In following sections, the details of each component of the model will be described.
The model of Mfb–M coupling
The Mfb–M coupling will be modeled based on [26], with the differential equations for the membrane potential of cardiac Mfb and myocyte are given by
where V_{Mfb,i} and V_{M} represent the transmembrane potential of the ith coupled Mfb and the human atrial myocyte, C_{m,Mfb} and C_{m,M} represent the membrane capacitance of the Mfb and the myocyte, I_{Mfb,i} and I_{M} represent the transmembrane current of the ith coupled Mfb and the human atrial myocyte, and G_{gap} represents the gapjunctional conductance. It is also noted that a negative I_{gap} [i.e., G_{gap}(V_{Mfb,i}–V_{M})] indicates that the current is flowing from the myocyte into the ith Mfb, and n is the total number of coupled Mfbs.
Mathematical model of the human atrial myocyte
The mathematical model of the human atrial myocyte developed by Maleckar et al. [50], which is based on experimental data and has correctly replicated APD restitution of the adult human atrial myocyte, was adopted in this study. To examine the influence of the stretch on myocyte AP, the original model from Maleckar et al. is modified with the total ionic current of myocyte (I_{M}) given as
where I_{Na} is fast inward Na^{+} current, I_{CaL} Ltype Ca^{2+} current, I_{t} transient outward K^{+} current, I_{Kur} sustained outward K^{+} current, I_{K1} inwardrectifying K^{+} current, I_{K,r} rapid delayed rectifier K^{+} current, I_{K,s} slow delayed rectifier K^{+} current, I_{B,Na} background Na^{+} current, I_{B,Ca} background Ca^{2+} current, I_{NaK} Na^{+}–K^{+} pump current, I_{CaP} sarcolemmal Ca^{2+} pump current, I_{NaCa} Na^{+}–Ca^{2+} exchange current, I_{SAC} stretchactivated current, and I_{Stim} stimulated current.
The model of I _{SAC}
Kuijpers et al. [55] have conducted experimental studies and reported that I_{SAC} in atrial myocytes is permeable to Na^{+}, K^{+}, and Ca^{2+} [33], and defined as
where I_{SAC,Na}, I_{SAC,K}, and I_{SAC,Ca} represent the contributions of Na^{+}, K^{+}, and Ca^{2+} to I_{SAC}, respectively. These currents are defined by the constantfield Goldman–Hodgkin–Katz current equation [56].
To introduce the effect of I_{SAC} on intracellular Na^{+}, K^{+}, and Ca^{2+} concentrations ([Na^{+}]_{i}, [K^{+}]_{i} and [Ca^{2+}]_{i}), we replace equations of [Na^{+}]_{i}, [K^{+}]_{i}, and [Ca^{2+}]_{i} in Maleckar et al.’s model [50] as
where F is Faraday’s constant, Vol_{i} cytosolic volume, I_{di} Ca^{2+} diffusion current from the diffusionrestricted subsarcolemmal space to the cytosol, I_{up} sarcoplasmic reticulum Ca^{2+} uptake current, I_{rel} sarcoplasmic reticulum Ca^{2+} release current, and O buffer occupancy.
The model of the Ca^{2+}–force relation
The model 4 of isometric force generation in cardiac myofilaments proposed by Rice et al. was adopted to model the Ca^{2+}–force relation [51, 52]. The concentration of Ca^{2+} bound to highaffinity or lowaffinity troponin sites is [HTRPNCa] and [LTRPNCa], respectively. The dynamics are governed as
where [HTRPN]_{tot} represents the total troponin highaffinity site concentration, and \(k_{\text{htrpn}}^{ + }\) and \(k_{\text{htrpn}}^{  }\) are the Ca^{2+} on and offrates for troponin highaffinity sites. [LTRPN]_{tot} represents the total troponin lowaffinity site concentration, and \(k_{\text{ltrpn}}^{ + }\) and \(k_{\text{ltrpn}}^{  }\) are the Ca^{2+} on and offrates for troponin lowaffinity sites.
The model of human atrial Mfb
The electrophysiological model of human atrial Mfb proposed by MacCannell et al. [26] was used in the present study. It includes time and voltagedependent K^{+} current (I_{Kv_Mfb}), inwardrectifying K^{+} current (I_{K1_Mfb}), Na^{+}–K^{+} pump current (I_{NaK_Mfb}), and Na^{+} background current (I_{B,Na_Mfb}).
In addition, I_{Na_Mfb} and I_{MGC_Mfb} are added in the Mfb model. According to our previous work [28], equations of I_{Na_Mfb} and I_{MGC_Mfb} are formulated as
where \(\overline{g}_{\text{Na,Mfb}}\) is the maximum conductance of I_{Na_Mfb} (0.756 nS), E_{Na,Mfb} the Nernst potential for Na^{+} ions, [Na^{+}]_{c,Mfb} the Mfb extracellular Na^{+} concentration (130.011 mM), [Na^{+}]_{i,Mfb} the Mfb intracellular Na^{+} concentration (the initial value is set as 8.5547 mM), and m_{Mfb} and j_{Mfb} the activation and inactivation parameters, respectively. To follow the experiment data [18], j has been modified as j^{0.12}. \(\overline{g}_{\text{MGC,Mfb}}\) is the maximum conductance of I_{MGC_Mfb} (0.043 nS), and E_{MGC,Mfb} is the reversal potential of MGCs (selected a value close to 0 mV) [21].
Mechanical behavior of a single segment
The mechanical behavior of a single segment in our model is based on the classical threeelement rheological scheme [53, 54].
As shown in Fig. 6, active force (F_{CE}) is generated by the contractile element (CE), and passive forces (F_{SE}, F_{PE}) are generated in a serial elastic element (SE) and a parallel elastic element (PE). F_{segment} is the total force generated by the segment. The element lengths are l_{CE}, l_{SE}, and l_{PE}. During mechanical equilibrium, F_{CE}, F_{segment}, and l_{PE} are defined as
Simulation protocol
We performed singlecell simulations with constant sarcomere length (isosarcometric contraction) and constant applied force (isotonic contraction) to investigate the effects of I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} on myocyte mechanical properties.
Five groups were simulated sequentially: one atrial myocyte without Mfb coupling (Group 1), one atrial myocyte coupled to two Mfbs without I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} (Group 2), one atrial myocyte coupled to two Mfbs with I_{Na_Mfb} (Group 3), one atrial myocyte coupled to two Mfbs with I_{SAC} and I_{Na_Mfb} (Group 4), and one atrial myocyte coupled to two Mfbs with I_{SAC}, I_{Na_Mfb}, and I_{MGC_Mfb} (Group 5).
First, simulations were carried out at a constant G_{gap} of 3 nS and a BCL of 1 s. Thereafter, the coupled system was paced with (1) BCLs from 0.1 to 2 s, (2) G_{gap} from 0.5 to 8 nS, and (3) number of coupled Mfbs from 1 to 8, to investigate the role of BCL, G_{gap}, and Mfbs in myocyte mechanical parameters. The maximum or minimum of F_{SE}, F_{PE}, F_{segment}, l_{CE}, l_{SE}, and l_{PE} at different BCL, G_{gap}, and Mfbs number were examined.
To ensure the coupled system reached steadystate, stimulation was repeated for 20 cycles. Results from the last cycle in each simulation were used for subsequent analyses. All state variables of the coupled model were updated by means of the forward Euler method. The time step was set to be 10 μs to ensure numerical accuracy and stability. More information on “Methods” is available in the Additional file 1.
Availability of data and materials
All data generated or analyzed during this study are included in this article.
Abbreviations
 SAC:

stretchactivated channel
 Mfb:

myofibroblast
 MGC:

mechanogated channel
 Mfb–M:

myofibroblast–myocyte
 VGSC:

voltagegated sodium channel
 AP:

action potential
 EMC:

electromechanical coupling
 MEF:

mechanoelectrical feedback
 TRPM7:

transient receptor potential cationic channel subfamily M member 7
 APD:

duration of the action potential
 BCL:

basic cycle length
 CE:

contractile element
 SE:

serial elastic element
 PE:

parallel elastic element
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Zhan, H., Zhang, J., Jiao, A. et al. Stretchactivated current in human atrial myocytes and Na^{+} current and mechanogated channels’ current in myofibroblasts alter myocyte mechanical behavior: a computational study. BioMed Eng OnLine 18, 104 (2019). https://doi.org/10.1186/s1293801907235
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DOI: https://doi.org/10.1186/s1293801907235
Keywords
 Mechanogated channels (MGCs)
 Myocyte mechanics
 Mathematical modeling
 Myofibroblast–myocyte (Mfb–M) coupling
 Stretchactivated channels (SACs)
 Voltagegated sodium channels (VGSCs)