Non-invasive Assessment of Myocardial Ischemia



Fig. 31.1
Concepts for non-invasive assessment of myocardial ischemia





31.2 Perfusion CT


The strength of perfusion imaging is visualizing the myocardial blood flow on which myocardial metabolism depends. Perfusion MR uses similar concept used in nuclear perfusion imaging or perfusion cardiac magnetic resonance imaging (CMR). From the myocardial and left ventricular cavity arterial input function or time-attenuation curves, the extent of regional myocardial perfusion is calculated or compared with the other regional myocardial perfusion. Perfusion is imaged in a complete cardiac cycle (dynamic perfusion imaging) or as a snapshot (static perfusion imaging). Scanners equipped with dual energy source can be used for perfusion imaging and mostly used for static perfusion imaging (Fig. 31.2). The performance of perfusion CT for predicting functionally significant stenosis is considered to be similar to nuclear perfusion imaging, stress CMR, or stress echocardiography, and is being validated against FFR [35]. Standard coronary angiography can be done along with perfusion imaging, which enables simultaneous anatomic evaluation of coronary arteries with functional evaluation of heart. Therefore, perfusion CT combined with coronary CT angiography can be a one-stop shop modality that assesses both anatomical and functional stenosis within a single session [6].

A430616_1_En_31_Fig2_HTML.gif


Fig. 31.2
Principle of myocardial perfusion CT . The difference between myocardial blood flow correlates with the myocardial up-slope normalized by arterial input function (AIF) up-slope, area under curve (AUC) of myocardial signal intensity up to AIF peak, or myocardial peak signal intensity. The difference between normal tissue and ischemic tissue is imaged as perfusion defect (line with red arrows)


31.2.1 Technical Aspect of Perfusion CT Imaging


Hyperemia is induced by pharmacological stress agents . Intravenous adenosine is widely used in a continuous dose of 140 μg/kg/min for 2 or 3 min. Regadenoson has longer plasma half time than adenosine and is administered in a single agent. Also it is a selective adenosine 2A receptor agonist and can be used in patients with asthma or airway disease. Dobutamine, a myocardial beta-1 agonist, or dipyridamole, adenosine receptor blocker, is not commonly used (Table 31.1).


Table 31.1
Stress agents for perfusion imaging

















































 
Advantage

Disadvantage

Exercise

Most physiological

Motion artifact → not practical for CT or MR

Least expensive

Effort-dependent

Adenosine

Current de facto standard

Potential bronchospasm (not good for chronic obstructive lung disease, asthma, caffeine user)

Tachycardia, AV block

Dipyridamole

Inexpensive

Prolonged effect

Tachycardia, AV block

May require aminophylline

Regadenoson, binodenoson

Bolus injection

Expensive

Fewer side effects in COPD/asthma

Prolonged effect

Tachycardia

Dobutamine

Physiological

Lower sensitivity/specificity

Tachycardia

Can provoke ischemia

Static or snap-shot perfusion CT assesses myocardial contrast distribution in a single time and doable in most CT scanners with lesser radiation exposure to dynamic perfusion CT. With sophisticated mathematical modeling, dynamic perfusion CT enables direct quantification of myocardial blood flow (MBF), myocardial blood volume, and myocardial flow reserve (Table 31.2). Regarding the diagnostic performance, static perfusion CT showed sensitivity = 0.85 (95% confidence interval = 0.70–0.93), specificity = 0.81 (0.59–0.93), area under curve = 0.90 (0.87–0.92) [7]. A recent dynamic perfusion CT showed comparable performance compared to CMR (Table 31.3) [820]. Also perfusion CT is better suited for quantification of myocardial blood flow than perfusion MR. Based on the nuclear perfusion studies, the nominal value of resting myocardial blood flow is known to be 0.9 ml/μg/min. The cut-off value of hemodynamically significant stenosis in perfusion CT was reportedly 0.75–0.78 ml/μg/min [16].


Table 31.2
Techniques for myocardial perfusion CT













































 
Strength

Weak points

Static perfusion CT

• Doable in most CT scanner

• Highly affected by image acquisition timing

• Doable with standard CCTA

• Minimal radiation (1–3 mSv)

• May need multiphase reconstruction to reduce artifacts (beam hardening, motion, partial scan artifacts)

• TPR (trans-myocardial perfusion ratio)

Dynamic perfusion CT

• Less susceptible to artifact

• Need specific scanner (256 or 320-slice, or 128-slice with shuttle mode)

• Quantitative blood flow analysis (myocardial blood flow or flow reserve)

• High radiation (>10 mSv)

• Axial coverage might be insufficient

• Need separated CCTA scanning

• Limited clinical data

Dual energy perfusion CT

• Iodine distribution map → better tissue discrimination

• Affected by image acquisition timing

• Quantitation of myocardial blood pool

• Needs standardization of iodine map interpretation

• Mostly static perfusion CT



Table 31.3
Diagnostic performance of perfusion CT

































































































































































































Study and publication

Techniques (Scanner)

N

Reference

Stenosis (%)

Sensitivity

Specificity

PPV

NPV

Basis of analysis

Rocha-Filho et al. [8]

Static (64-DSCT)

35

ICA

50

91

91

86

93

Vessel

70

91

78

53

97

Feuchtner et al. [9]

Static (128-DSCT)

25

ICA

70

100

74

97

100

Vessel

Nasis et al. [10]

Static (320-MDCT)

20

SPECT/ICA

50

94

98

94

98

Vessel/territory

70

79

91

73

93

Carrascosa et al. [11]

Static, rapid kV switching

25

SPECT


73

95



Vessel

Magalhaes et al. [12]

Static (320-MDCT)

381

ICA + SPECT,MR

50

98

96

98

96

Territory

58

86

87

55

Vessel

Huber et al. [13]

Static (256-MDCT)

32

ICA

50

76

100

90

100

Vessel

Rossi et al. [14]

Dynamic (128-DSCT)

80

ICA

50

78

75

91

51

Territory

88

90

98

77

Vessel

Bamberg et al. [15]

Dynamic (128-DSCT)

33

FFR

50

93

87

75

97

Vessel

Bamberg et al. [16]

Dynamic (128-DSCT)

31

Cardiac MR


100

75

100

92

Vessel

Ko et al. [17]

Dynamic (64-DSCT)

45

ICA

50

93

86

88

91

Vessel

Wang et al. [18]

Dynamic (128-DSCT)

30

ICA/SPECT

50

90

81

58

97

Vessel/territory

Kim et al. [19]

Dynamic (128-DSCT)

50

Cardiac MR


77

94

53

98

Vessel/territory

Wichmann et al. [20]

Dynamic (128-DSCT)

71

Visual assessment

50

100

88

100

43

Territory


31.3 Computational Simulation of Fractional Flow Reserve


Increase of myocardial blood flow by 2 to 3-fold is required to match the increased need of cardiac output in most activities. Coronary microvessel accounts for most resistance or pressure drop in coronary circulation. The increase of myocardial blood flow is mainly controlled by decrease in microvascular resistance. Therefore functionally significant epicardial coronary artery stenosis can be defined by failure to increase blood flow during hyperemia which induces maximal dilatation of resistance vessel. Fractional flow reserve (FFR) is defined by the ratio of hyperemic coronary flow through stenotic vessel to the hypothetical normal vessel. Because flow is proportional to pressure in fixed stenosis, FFR can be measured by average pressure gradient. Pressure drop of more than 20% or FFR ≤ 0.80 is widely advocated as a gold standard of vessel-specific physiologically significant stenosis which may evoke myocardial ischemia.

FFR is measured during invasive cardiac catheterization and requires insertion of a pressure wire inserted through the stenosis. There may be and instability of measurement and signal shift. Placement of a pressure wire near the stenosis or pressure recovery zone may lead to overestimation of FFR. A non-invasive simulation of FFR would be very valuable to avoid these procedural shortcomings and the expense of pressure wire and invasive cardiac catheterization.


31.3.1 Computation of Simulated FFR


Like the other fluid systems, blood flow in the cardiovascular system is ruled by the physical laws of mass conservation, momentum conservation, and energy conservation. Therefore it can be calculated by mathematical models. For patient-specific coronary circulation, 3-dimensional numerical models based on computational flow dynamics which can compute complex flow patterns are preferred to zero dimensional models or lumped parameter model which is employed in large systemic vessels. Computational FFR is derived based on the regional physical geometry, the boundary condition which is the behavior and properties at the boundaries of the region, and the physical laws of fluid in the region.

FFR can be described as a pressure gradient across stenotic segment during maximal hyperemia. Anatomical stenosis, myocardial mass, and microvascular resistance constitute FFR value and can be calculated from patient-specific sophisticated coronary arterial anatomical model, vessel-specific myocardial mass, and microvascular resistance which determine the outlet boundary condition [21, 22]. CT images provide patient-specific anatomy model of local geometry, individual coronary artery morphology, volume, and myocardial mass. From these data, cardiac output and baseline coronary blood flow can be calculated by using allometric scaling laws [2325]. This computational approach was derived from a general model that describes the transport of essential materials through space-filling fractal branched networks, and is based on a form-function relationship [26]. The diameter-flow rate relation is determined according to Murray’s law [27] and Poiseuille’s equation, which considers shear stress on the endothelial surface and remodeling to maintain homeostasis [28]. Morphometry laws are also adapted to obtain the physiological resistance to flow aroused by coronary artery branches [29]. Microvascular resistance at baseline and during maximal hyperemia, which is fundamental for FFR measurement, can be approximated using population-based data on the effect of adenosine on coronary flow [30] (Fig. 31.3).

A430616_1_En_31_Fig3_HTML.jpg


Fig. 31.3
Concept of computational FFR


31.3.2 Clinical Results of Computational FFR


Landmark trials including DISCOVER-FLOW [31], DeFACTO [32], and NXT [33] showed that FFR-CT, a proprietary computational FFR, showed high diagnostic performance in discriminating ischemia in patients who had intermediate coronary artery stenosis. The NXT trial reported sensitivity and negative predictive value of FFR-CT in diagnosis of ischemia (defined as invasive FFR < 0.80) in patients with intermediate stenosis severity were 80% and 92%, respectively [33]. In a recent meta-analysis of FFR-CT based on 833 patients and 1377 vessels, FFR-CT showed a moderate diagnostic performance for identification of ischemic vessel with pooled sensitivity = 84% and specificity = 76% at a per-vessel basis [34] (Table 31.4). The PLATFORM study showed that a decision-making strategy using CCTA with FFR-CT was associated with clinical outcomes comparable to using invasive FFR and a 33% cost reduction [35]. Therefore, FFR-CT can effectively rule out intermediate lesions that cause ischemia and could also reduce the unnecessary ICA and invasive FFR.


Table 31.4
Results of non-invasive computational FFR technologies





















































































































Study

Technology

N of vessels

Sensitivity (%)

Specificity (%)

PPV (%)

NPV (%)

Accuracy (%)

Area under curve, per vessel

Correlation coefficient compared with FFR

Computation time

FFR-CT, DISCOVER-FLOW, Koo et al. [31]

Heartflow ver 1.0

159

88

82

74

92

84

0.90

0.72

Hours, off-site

FFR-CT, DeFACTO, Min et al. [32]

Heartflow ver 1.2

408

80

63

56

84

69

0.81

0.63

Hours, off-site

FFR-CT, NXT, Norgaard et al. [33]

Heartflow ver 1.4

484

84

87

62

95

86

0.93

0.82

Hours, off-site

FFR-CT, Kim et al. [19]

Heartflow ver 1.2

48

85

57

83

62

77


0.60

Hours, off-site

cFFR

Siemens cFFR ver 1.4

67

85

85

71

93

85

0.92

0.66

<1 h, standalone

cFFR

Siemens cFFR ver 1.4

189

88

65

65

88

75

0.83

0.59

<1 h, standalone

cFFR

Siemens cFFR ver 1.7

23

83

76

56

93

78


0.77

<1 h, standalone

Pooled analysis


1330

84

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Jan 19, 2018 | Posted by in CARDIOLOGY | Comments Off on Non-invasive Assessment of Myocardial Ischemia

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