Re: 건생병사로 난치병 증상 호전 --＞ 호전의 과학적 변수탐구.. inbody검사!!

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Sensors (Basel)

. 2014 Jun 19;14(6):10895–10928. doi: 10.3390/s140610895

The Theory and Fundamentals of Bioimpedance Analysis in Clinical Status Monitoring and Diagnosis of Diseases

Sami F Khalil 1,2,3, Mas S Mohktar 1,2, Fatimah Ibrahim 1,2,*

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PMCID: PMC4118362  PMID: 24949644

Abstract

Bioimpedance analysis is a noninvasive, low cost and a commonly used approach for body composition measurements and assessment of clinical condition. There are a variety of methods applied for interpretation of measured bioimpedance data and a wide range of utilizations of bioimpedance in body composition estimation and eval‎uation of clinical status. This paper reviews the main concepts of bioimpedance measurement techniques including the frequency based, the allocation based, bioimpedance vector analysis and the real time bioimpedance analysis systems. Commonly used prediction equations for body composition assessment and influence of anthropometric measurements, gender, ethnic groups, postures, measurements protocols and electrode artifacts in estimated values are also discussed. In addition, this paper also contributes to the deliberations of bioimpedance analysis assessment of abnormal loss in lean body mass and unbalanced shift in body fluids and to the summary of diagnostic usage in different kinds of conditions such as cardiac, pulmonary, renal, and neural and infection diseases.

초록

생체 임피던스 분석은 

비침습적이고, 비용이 저렴하며, 

임상 상태의 평가와 신체 구성 측정을 위해 흔히 사용되는 접근법입니다. 

측정된 생체 임피던스 데이터의 해석에 적용되는 

다양한 방법과 신체 구성 추정에 대한 생체 임피던스의 광범위한 활용, 

그리고 임상 상태의 평가가 있습니다. 

이 논문은 

주파수 기반, 할당 기반, 생체 임피던스 벡터 분석, 

실시간 생체 임피던스 분석 시스템 등 생체 임피던스 측정 기법의 주요 개념을 검토합니다. 

또한, 

체성분 평가를 위한 일반적으로 사용되는 

예측 방정식과 인체 측정, 성별, 인종, 자세, 측정 프로토콜, 전극 인공물 등이 

추정값에 미치는 영향에 대해서도 논의합니다. 

또한, 

이 논문은 제지방량 감소와 체액 불균형 변화의 비정상적인 손실에 대한 

생체 임피던스 분석 평가와 심장, 폐, 신장, 신경 및 감염성 질환과 같은 

다양한 종류의 조건에서 진단적 사용에 대한 요약에 기여합니다.

Keywords: bioimpedance analysis, body composition, clinical status monitoring, diseases diagnostic and prediction

1. Introduction

Bioimpedance analysis is a broadly applied approach used in body composition measurements and healthcare assessment systems. The essential fundamentals of bioimpedance measurement in the human body and a variety of methods are used to interpret the obtained information. In addition there is a wide spectrum of utilization of bioimpedance in healthcare facilities such as disease prognosis and monitoring of body vital status. Thus, with such a broad utilization, we feel that this warrants a review of the most fundamental aspects and healthcare applications of bioimpedance analysis.

Studies on the electrical properties of biological tissues have been going on since the late 18th century [1]. Thomasset [2] explored the utilization of bioimpedance measurement in total body water estimation using needle electrodes. Nyboer [3] applied quad surface electrode readings for bioimpedance measurements to estimate the fat free mass of the human body. Hoffer [4] introduced the association between total body impedance and total body water content in reference to tritium dilution techniques.

The electrical properties of biological tissues are currently categorized based on the source of the electricity, i.e., active and passive response. Active response (bioelectricity) occurs when biological tissue provokes electricity from ionic activities inside cells, as in electrocardiograph (ECG) signals from the heart and electroencephalograph (EEG) signals from the brain. Passive response occurs when biological tissues are simulated through an external electrical current source [5]. Bioimpedance or biological impedance is defined as the ability of biological tissue to impede electric current [6].

Due to the noninvasiveness, the low cost and the portability of bioimpedance analysis systems, numerous researchers have conducted studies on bioimpedance analysis and its applications in body composition estimation and eval‎uation of clinical conditions. Recently, Mialich et al. [7] reviewed the applications of bioimpedance analysis in body composition assessment and monitoring of chronic diseases with a comprehensive listing of the most used equations, however, recent techniques such as real time multi-sine bioimpedance analysis and bioimpedance vector analysis methods were not discussed. Lukaski [8] has revised the conceptual modules of bioimpedance analysis for physiological activities assessment and diseases prognosis. The study states that the applied multiple regression approaches and physical modules in bioimpedance analysis have limited utilization in individuals' measurement. This paper is a review of the basic fundamentals and the applications of bioimpedance analysis. The first section highlights the main bioimpedance measurement approaches using single frequency, multiple frequencies and broadband frequency spectrum signals, in addition to applied bioimpedance measurements method across the whole body, through body segments and other alternative analysis method such as vector bioimpedance analysis and real time bioimpedance methods. Body composition parameters, which include lean mass and fluid volumes estimation using bioimpedance measurements, are discussed in the second section. Basic factors in bioimpedance measurements, including anthropometric measurements, age, race, protocols and postures, and shape and artifacts of electrode are discussed in the third section. Finally, applications of bioimpedance analysis in diseases prognosis and clinical monitoring systems are outlined in the fourth section.

1. 소개

생체 임피던스 분석은 체성분 측정 및 건강 관리 평가 시스템에 널리 사용되는 접근 방식입니다. 인체 생체 임피던스 측정의 기본 원리와 다양한 방법이 사용되어 얻은 정보를 해석합니다. 또한 질병 예후 및 신체 활력 상태 모니터링과 같은 의료 시설에서 생체 임피던스를 광범위하게 활용합니다. 따라서 이러한 광범위한 활용을 고려할 때, 생체 임피던스 분석의 가장 기본적인 측면과 의료 응용에 대한 검토가 필요하다고 생각합니다.

생물학적 조직의 전기적 특성에 대한 연구는 18세기 후반부터 진행되어 왔습니다 [1]. Thomasset [2]은 바늘 전극을 사용하여 전신 수분량을 추정하는 데 생체 임피던스 측정의 활용을 탐구했습니다. Nyboer [3]은 생체 임피던스 측정을 위해 4면 전극 판독값을 적용하여 인체의 무지방 질량을 추정했습니다. Hoffer [4]는 삼중수소 희석 기법을 참조하여 전신 임피던스와 전신 수분 함량 간의 연관성을 소개했습니다.

현재 생물학적 조직의 전기적 특성은 전기의 원천, 즉 능동적 반응과 수동적 반응에 따라 분류됩니다. 능동적 반응(생체전기)은 심장의 심전도(ECG) 신호나 뇌의 뇌파(EEG) 신호처럼 생물학적 조직이 세포 내부의 이온 활동으로부터 전기를 유발할 때 발생합니다. 수동적 반응은 외부 전류원을 통해 생물학적 조직을 자극할 때 발생합니다 [5]. 생체 임피던스 또는 생물학적 임피던스는 전류를 방해하는 생물학적 조직의 능력을 의미합니다 [6].

생체 임피던스 분석 시스템은 비침습적이며, 비용이 저렴하고 휴대성이 뛰어나기 때문에, 수많은 연구자들이 생체 임피던스 분석과 체성분 추정 및 임상 상태 평가에서의 그 적용에 대한 연구를 수행해 왔습니다. 최근 Mialich 외. [7]은 가장 많이 사용되는 방정식의 포괄적인 목록을 통해 체성분 평가 및 만성 질환 모니터링에 생체 임피던스 분석의 적용을 검토했지만, 실시간 다중 사인 생체 임피던스 분석 및 생체 임피던스 벡터 분석 방법과 같은 최신 기술은 논의되지 않았습니다. Lukaski [8]는 생리학적 활동 평가와 질병 예후를 위한 생체 임피던스 분석의 개념적 모듈을 개정했습니다. 이 연구에 따르면, 생체 임피던스 분석에 적용된 다중 회귀 분석 접근법과 물리적 모듈은 개인 측정에서 활용도가 제한적이라고 합니다. 이 논문은 생체 임피던스 분석의 기본 원리와 응용에 대한 리뷰입니다.

첫 번째 섹션에서는

단일 주파수, 다중 주파수, 광대역 주파수 스펙트럼 신호를 사용하는 주요 생체 임피던스 측정 접근법,

전신에 걸친 생체 임피던스 측정 방법,

신체 부위별 생체 임피던스 측정 방법,

벡터 생체 임피던스 분석,

실시간 생체 임피던스 방법 등 기타 대체 분석 방법을 중점적으로 다룹니다.

생체 임피던스 측정을 이용한

제지방량 및 체액량 추정 등 체성분 매개변수는

두 번째 섹션에서 다룹니다.

인체 측정, 나이, 인종, 프로토콜과 자세, 전극의 형태와 인공물 등

생체 임피던스 측정의 기본 요인에 대해서는 세 번째 섹션에서 설명합니다.

마지막으로,

질병 예후와 임상 모니터링 시스템에 생체 임피던스 분석의 적용에 대해서는

네 번째 섹션에서 간략하게 설명합니다.

2. Fundamentals of Bioimpedance Measurement Techniques

Impedance (Z), from an electrical point of view, is the obstruction to the flow of an alternating current and, hence, is dependent on the frequency of the applied current, defined in impedance magnitude (|Z|) and phase angle (φ) as shown in Equations (1)–(3) [9]. Bioimpedance is a complex quantity composed of resistance (R) which is caused by total body water and reactance (Xc) that is caused by the capacitance of the cell membrane [5]:

2. 생체 임피던스 측정 기법의 기초

전기적 관점에서 임피던스(Z)는

교류 전류의 흐름을 방해하는 요소이며,

따라서 적용된 전류의 주파수에 따라 달라집니다.

임피던스 크기(|Z|)와 위상 각도(φ)는 방정식 (1)-(3)에 정의되어 있습니다 [9].

생체 임피던스는

전신 수분으로 인한 저항(R)과 세포막의 용량으로 인한 리액턴스(Xc)로 구성된 복잡한 양입니다 [5]:

𝑍=𝑅+𝑗⁢𝑋𝑐

(1)

|𝑍|=√𝑅2+𝑋2𝑐

(2)

𝛷=tan−1⁡(𝑋𝑐𝑅)

(3)

Resistance of an object is determined by a shape, that is described as length (L) and surface area (A), and material type, that is described by resistivity (ρ), as shown in Equation (4), [9]. Reactance (Xc) of an object as shown in Equation (5), is defined as resistance to voltage variation across the object and is inversely related with signal frequency (f) and capacitance (C) [9]. In biological systems resistance is caused by total water across the body, and reactance occurs due to the capacitance of the cell membrane [5,10]:

물체의 저항은 방정식 (4)에 나타난 것처럼 길이(L)와 표면적(A)로 설명되는 모양과 저항률(ρ)로 설명되는 재료 유형에 의해 결정됩니다. 방정식 (5)에 나타난 바와 같이, 물체의 리액턴스(Reactance, Xc)는 물체 전체에 걸친 전압 변화에 대한 저항으로 정의되며, 신호 주파수(f)와 커패시턴스(C)와 반비례합니다 [9]. 생물학적 시스템에서 저항은 몸 전체에 걸친 총 물의 양에 의해 발생하며, 리액턴스는 세포막의 커패시턴스로 인해 발생합니다 [5,10]:

𝑅(𝑜ℎ𝑚)=𝜌(𝛺.𝑚)⁢𝐿(𝑚)𝐴(𝑚2)

(4)

𝑋𝑐⁡(𝑜ℎ𝑚)=12⁢𝜋⁢𝑓(𝐻⁡𝑧)⁡𝐶(𝐹𝑎𝑟𝑎𝑑)

(5)

Capacitance (C) is defined as the ability of the non-conducting object to save electrical charges, that is equal to the ratio between differentiation in voltage across object (dV/dt) and current that is passed through the object (I(t)), as shown in Equation (7). In the parallel capacitor module, capacitance is in direct proportion to the surface area (A) in meters square and inversely proportional to distance (d) in meters between the charged plates, and is dependent on the permittivity constant of vacuum (ε0 ≈ 8.854 × 10−12 F·m−1) and the relative dielectric permittivity constant (εr) that is defined based on the material between the plates (for a vacuum space, εr = 1), as shown in Equation (6) [9]:

용량(C)은 전하를 저장하는 비전도성 물체의 능력을 의미하며, 방정식 (7)에 표시된 바와 같이 물체 양단의 전압 차이(dV/dt)와 물체를 통과하는 전류(I(t))의 비율과 같습니다. 병렬 커패시터 모듈에서, 커패시턴스는 표면적(A)에 정비례하고, 전하를 띤 플레이트 사이의 거리(d)에 반비례하며, 진공의 유전율 상수에 의존합니다(ε0 ≈ 8.8 54 × 10−12 F·m−1)과 판 사이의 재료에 기초하여 정의되는 상대 유전율 상수(εr) (진공 공간인 경우, εr = 1)는 식 (6) [9]에 나와 있습니다.

𝐶(𝐹𝑎𝑟𝑎𝑑)=ɛ0⁢ɛ𝑟⁢𝐴(𝑚3)𝑑(𝑚)

(6)

𝐶(𝐹𝑎𝑟𝑎𝑑)=𝑑⁢𝑉⁡(𝑡)𝑑⁢𝑡/𝐼⁡(𝑡)

(7)

Body composition estimation using bioimpedance measurements is based on determination of body volume (Vb) through the basic means of resistance measurement. From Equation (4) that gives the relation between resistance and ratio of length (L) to surface area (A), body volume (Vb) can be obtained by substituting the surface area (A) with the numerator and denominator of the length (L), as in Equation (8):

생체 임피던스 측정을 이용한 체성분 추정법은 저항 측정의 기본 수단을 통해 체적(Vb)을 결정하는 것을 기반으로 합니다. 저항과 길이(L) 대 표면적(A)의 비율 사이의 관계를 나타내는 방정식 (4)에서, 표면적(A)을 길이의 분자와 분모로 대체하면 체적(Vb)을 구할 수 있습니다(방정식 (8) 참조).

𝑉𝑏⁡(𝑚3)=𝜌(𝛺.𝑚)⁢𝐿2(𝑚)𝑅(𝑜ℎ𝑚)

(8)

The human body as a volume is composed generally of fat mass (FM) which is considered as a non-conductor of electric charge and is equal to the difference between body weight (WtBody) and fat free mass (FFM), as shown in Equation (9); and FFM, which is considered as the conducting volume that helps the passing of electric current due to conductivity of electrolytes dissolved in body water. Studies show that water, known as total body water (TBW) is the major compound of FFM and is equal to 73.2% in normal hydration subjects, as in Equation (10) [11]:

인체는 체중(WtBody)과 체지방량(FFM)의 차이로 계산되는 체지방량(FM)으로 구성되어 있으며, 이는 전기 전도체가 아닌 것으로 간주됩니다(방정식 (9) 참조). 그리고 체수(WtWater)에 용해된 전해질의 전도성으로 인해 전류의 흐름을 돕는 전도체인 체지방량(FFM)으로 구성되어 있습니다. 연구에 따르면, TBW(총 체수분)로 알려진 물은 FFM의 주요 구성 요소이며, 정상적인 수분 공급을 받은 피실험자의 경우 73.2%에 해당한다고 합니다. 방정식 (10) [11]:

𝐹𝑀=𝑊⁢𝑡𝐵𝑜𝑑𝑦−𝐹𝐹𝑀

(9)

𝑇𝐵𝑊=0.73⁢𝐹𝐹𝑀

(10)

In bioimpedance measurements, the human body is divided into five inhomogeneous segments, two for upper limbs, two for lower limbs and one for the trunk. In the five compartment module, the human body is composed of FM and FFM which consists of bone minerals and body cell mass (BCM) that include protein and total body water that consists of extracellular fluid (ECF) and intracellular fluid (ICF) [5]. Figure 1, shows the five segments and compartments of human body.

생체 임피던스 측정에서 인체는 상지, 하지, 몸통의 세 부분으로 나뉘어집니다. 다섯 구획 모듈에서, 인체는 뼈의 무기질과 단백질을 포함하는 체세포 질량(BCM)과 세포 외액(ECF)과 세포 내액(ICF)으로 구성된 전신 수분으로 구성된 FM과 FFM으로 구성되어 있습니다 [5]. 그림 1은 인체의 다섯 부분과 구획을 보여줍니다.

Figure 1.

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Main body segments and compartments.

Most of the known prediction methods rely on the relation between water volume and the ratio between square length to resistance (L2/R) [12], however the alternation in anatomical and anthropometric features of the whole human body and segments cause variations in estimated volumes. Jaffrin and Morel reviewed that most TBW estimation equations between 1985 and 1994 were based on values predicted using the H2/R50 that was introduced by Kyle et al. [13,14] and Houtkouper et al. [15].

주요 신체 부위와 구획.

대부분의 알려진 예측 방법은 물의 부피와 제곱 길이 대 저항 비율(L2/R) [12] 사이의 관계에 의존하지만, 인체 전체와 부위의 해부학적 및 인체 측정학적 특징의 변화는 추정 부피의 차이를 유발합니다. Jaffrin과 Morel은 1985년과 1994년 사이에 대부분의 TBW 추정 방정식이 Kyle 등의 연구에서 소개된 H2/R50을 사용하여 예측된 값을 기반으로 한다는 것을 검토했습니다. [13,14] 그리고 Houtkouper 등의 연구 [15].

Measurement of bioimpedance is obtained from the whole body and body segments separately, using single frequency, multiple frequencies and bioimpedance spectroscopy analysis. In addition to several alternative assessments method such as bioimpedance vector analysis and real time bioimpedance analysis.

생체 임피던스 측정은 단일 주파수, 다중 주파수, 생체 임피던스 분광 분석을 사용하여 전신과 신체 부위별로 측정합니다. 생체 임피던스 벡터 분석 및 실시간 생체 임피던스 분석과 같은 여러 가지 대체 평가 방법 외에도.

2.1. Single Frequency Bioimpedance Analysis (SF-BIA)

Analysis of bioimpedance information obtained at 50 KHz electric current is known as single-frequency bioimpedance analysis (SF-BIA). SF-BIA is the most used and is one of the earliest proposed methods for the estimation of body compartments, It is based on the inverse proportion between assessed impedance and TBW, that represents the conductive path of the electric current [5,16].

SF-BIA predicts the volume of TBW that is composed of fluctuating percentages of extra cellular fluid (ECF) which is almost equal to 75% of TBW, and ICF that represent the rest [5]. SF-BIA instruments have been used to assess TBW and FFM using the derived Equations (2) and (3), respectively, for normal hydrated subjects, although SF-BIA is not valid for body conditions with significantly altered hydration [17]. Studies by Hanai [18] on mixture theory report that body tissue conductivity is diverse [5], and SF-BIA shows limitations in ICF variance prediction, however many of studies show an acceptable correlation in ICF estimation [19].

2.1. 단일 주파수 생체 임피던스 분석(SF-BIA)

50KHz 전류에서 얻은 생체 임피던스 정보의 분석은 단일 주파수 생체 임피던스 분석(SF-BIA)으로 알려져 있습니다. SF-BIA는 가장 많이 사용되고 있으며, 신체 구획을 추정하는 데 가장 먼저 제안된 방법 중 하나입니다. 이는 전류의 전도 경로를 나타내는 평가된 임피던스와 TBW 사이의 역비율을 기반으로 합니다 [5,16].

SF-BIA는 TBW의 75%에 해당하는 세포 외액(ECF)과 나머지 5%를 차지하는 세포 내액(ICF)의 변동하는 비율로 구성된 TBW의 양을 예측합니다. SF-BIA 기기는 정상적인 수분 공급 상태를 가진 피험자에 대해 각각 도출된 방정식 (2)과 (3)을 사용하여 TBW와 FFM을 평가하는 데 사용되어 왔지만, SF-BIA는 수분 공급 상태가 크게 변한 신체 상태에는 유효하지 않습니다 [17]. 혼합 이론에 대한 Hanai의 연구 [18]에 따르면 신체 조직의 전도도는 다양하다고 보고하고 있으며 [5], SF-BIA는 ICF 분산 예측에 한계가 있는 것으로 나타났지만, 많은 연구에서 ICF 추정에 있어 수용 가능한 상관 관계를 보여주고 있습니다 [19].

2.2. Multiple Frequency Bioimpedance Analysis (MF-BIA)

Analysis of bioimpedance that is obtained at more than two frequencies is known as multiple-frequency bioimpedance analysis (MF-BIA). MF-BIA is based on the finding that the ECF and TBW can be assessed by exposing it to low and high frequency electric currents, respectively. Thomasset [2] has proposed TBW and ECF estimation using 100 and 1 kHz based on the Cole model [20]. However, in later years, Jaffrin et al. [21] stated that technically a bioimpedance analyzer should use frequency range between 5–1000 kHz. Simpson et al. [22] state that low frequency in MF-BIA is generally less than 20 KHz and high frequency is more than 50 KHz. Hannan et al. [23] report that parameters measured using a frequency of less than 5 KHz and more than 200 KHz fluctuate around the actual value and conclude that estimated TBW is more accurate using the MF-BIA than the BIS method with the same predicted values of ECF for both methods. Patel et al. [24] reported that in diseased subjects, TBW prediction using SF-BIA gave more precise results than MF-BIA. In general, the MF-BIA method predicts ECF more precisely than the SF-BIA method; however in elderly diseased subjects the MF-BIA method shows less sensitivity in detecting fluid shifts between ECF and ICF [19].

2.2. 다중 주파수 생체 임피던스 분석(MF-BIA)

2개 이상의 주파수에서 얻은 생체 임피던스 분석은 다중 주파수 생체 임피던스 분석(MF-BIA)으로 알려져 있습니다. MF-BIA는 ECF와 TBW가 각각 저주파와 고주파 전류에 노출시켜 평가할 수 있다는 발견에 기초합니다. Thomasset [2]은 콜 모델 [20]을 기반으로 100kHz와 1kHz를 사용하여 TBW와 ECF 추정치를 제안했습니다. 그러나, 이후에 Jaffrin 등은 [21] 기술적으로 생체 임피던스 분석기는 5-1000kHz 사이의 주파수 범위를 사용해야 한다고 주장했습니다. Simpson 등은 [22] MF-BIA의 저주파는 일반적으로 20kHz 미만이고, 고주파는 50kHz 이상이라고 주장했습니다. Hannan et al. [23]은 5KHz 미만의 주파수와 200KHz 이상의 주파수를 사용하여 측정된 매개변수가 실제 값을 중심으로 변동한다고 보고하고, 두 방법 모두에 대해 동일한 ECF 예측값을 사용하는 BIS 방법보다 MF-BIA를 사용하는 것이 추정 TBW를 더 정확하게 추정한다고 결론을 내립니다. Patel et al. [24]은 병이 있는 피실험자에서 SF-BIA를 이용한 TBW 예측이 MF-BIA보다 더 정확한 결과를 제공한다고 보고했습니다. 일반적으로, MF-BIA 방법은 SF-BIA 방법보다 ECF를 더 정확하게 예측합니다. 그러나 노인이 병이 있는 피실험자에서 MF-BIA 방법은 ECF와 ICF 사이의 체액 이동을 감지하는 데 덜 민감합니다 [19].

2.3. Bioimpedance Spectroscopy (BIS)

Analysis of bioimpedance data obtained using a broad band of frequencies is known as bioimpedance spectroscopy (BIS). The BIS method is based on the determination of resistance at zero frequency (R0) and resistance at infinity frequency (Rinf) that is then used to predict ECF and TBW, respectively. The use of 100 and 1 kHz, respectively, was earlier proposed by Thomasset [25] who applied the basics of Hanai's mixture theory [18] and Cole's module [26,27] as explained by the Cole-Cole plot (Figure 2), however it is complicated to directly measure these values because of the relaxation phenomena of living tissue [20].

2.3. 생체 임피던스 분광법(BIS)

광범위한 주파수 대역을 사용하여 얻은 생체 임피던스 데이터의 분석은 생체 임피던스 분광법(BIS)으로 알려져 있습니다. BIS 방법은 각각 ECF와 TBW를 예측하는 데 사용되는 제로 주파수(R0)에서의 저항과 무한대 주파수(Rinf)에서의 저항을 결정하는 것에 기초합니다. 100kHz와 1kHz를 각각 사용하는 것은 한아이의 혼합물 이론(Hanai's mixture theory) [18]과 콜의 모듈(Cole's module) [26,27]의 기본 원리를 콜-콜 플롯(Cole-Cole plot) (그림 2)에 따라 적용한 톰아셋(Thomasset) [25]에 의해 이전에 제안된 바 있습니다. 그러나 살아 있는 조직의 이완 현상 때문에 이 값을 직접 측정하는 것은 복잡합니다 [20].

Figure 2.

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Cole-Cole module plot and Cole module parameters.

Reference methods for estimating TBW are based on radioisotopic dilution of deuterium, and for ECF estimation they are based on the dilution of bromide [28] and for ICF they are based on the radioactive potassium isotope, 40K, both elements which are readily diffused in the human body [29,30]. Reference techniques are invasive, expensive and complicated when compared to bioimpedance methods, although the precision is dependent on the electrical module and body parameter variation [21].

Estimation of TBW, ECF and ICF using BIS techniques can be performed using either an equation modules approach [10,31–33] or an analytically derived equations approach [27]. Hanai's mixture theory shows limitations in some studies [14,15,34], however it showed advantages in other studies [35,36]. Ward et al. [37] stated that the differences in biological construction among subjects may limit mixture theory as noted in some studies [38,39]. Scharfetter et al. [40] report that an accurate module for body fluid allocation and trusted fitting methods are most crucial factors in the BIS method.

The determination of Cole module parameters (R0, Rinf, α, Fc), in Figure 2 is done using the BIS method which is based on the argument that the human body is composed of a mixture containing conducting and non-conducting compartments [18].

In Equation (4), the reference method is based on the assumption that the measured resistance (R) represents the total conducting volume of the lean body mass. However in the BIS method, the measured resistance represents the total conducting and non-conducting part of the lean body mass, so that the non-conducting part is included by multiplying the obtained resistance by body shape factor (Kb) and substituting the surface area (A) by body volume (Vb). Ayllon et al. [41] reports that the estimation of Cole module parameters (R0, Rinf, α, Fc) that is obtained by using only resistance achieves slightly better results and there is less standard error based on the Non-Linear Least Squares technique as compared to the capacitive and impedance complex components. Ward et al. [42] concludes that the Cole parameters can be obtained by using four selected frequencies and substituting a fitting technique based on amplitude impedance values at these frequencies:

𝑅=𝐾𝑏⁢𝜌⁢𝐻⁡𝑡2𝑉𝑏

(11)

where, R is resistance, ρ is resistivity, Ht is the human height, Vb is the body volume and Kb is a dimensionless shape factor calculated from the length and perimeters of the upper and lower limbs, and the trunk, taken into consideration the body shape composed of the five cylinders.; Van Loan et al. [43] calculated the shape factor (Kb) from statistical anatomical measurements in adults to be equal to 4.3.

2.4. Whole Body Bioimpedance Measurement

Measurement of total body bioimpedance is the most commonly used method for estimating whole body compartments. Many of the whole body bioimpedance instruments apply three approaches for impedance measurement: hand to foot method [14,17], foot to foot [44–46] method and hand to hand method [47,48]. The hand to foot (Figure 3a) one is the most commonly used method. It was introduced by Hoofer [4] and later revised by Nyboer [3] to decrease the contact impedance between skin and electrodes, and validated by Lukaski [17] in 140 normal adults. Tetrapolar hand to foot measurements are performed on a supine subject for 15 min, placing electrodes filled with gel to minimize gap impedance on the dorsal surfaces of the right hand and foot, distal (current) ones being respectively proximal to the metacarpal and metatarsal phalangeal joints, in accordance with standard tetrapolar electrode placement [49]. Foot to foot measurements (Figure 3b) were introduced by Nuñez et al. [50] through the use of a pressure-contact foot-pad electrode. In leg to leg bioimpedance measurements, the subject stands vertically, with uncovered feet, on four stainless steel footpads electrodes and divided for each foot into frontal and back portion for current injecting and voltage measurement [46]. Hand to hand bioimpedance measurements were introduced by Ghosh et al. [48] by performing body composition analyses using a handheld impedance meter in subjects with malnutrition. The device was held while both arms were stretched out horizontally in front of the body. Deurenberg et al. [47] validated the hand to hand method on 298 Singaporean subjects and reported that readings obtained using a handheld impedance meter were significantly acceptable for those subjects.

Figure 3.

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Whole body bioimpedance measurement techniques, (a) hand to foot and (b) foot to foot electrodes positioning.

2.5. Body Segment Bioimpedance Measurement

Segmental bioimpedance analysis achieves better estimation of skeletal muscle mass (SMM) than whole body bioimpedance analysis, with a reported standard error of 6.1% in reference to MRI measurements among 30 male subjects [51]. Baumgartner et al. [52] stated that multi-frequency segmental bioimpedance analysis enhances and elucidates the relationship between bioimpedance analysis and body compartment estimation after examining the impact of phase angle on body composition prediction among 116 normal subjects.

Segmental bioimpedance analysis detects the fluctuation in ECF due to differences in posture and is more precise than the ankle foot method [53], and gives a better estimation of TBW than total body measurements with reference to dilution method [54].

Segmental or perpendicular bioimpedance analysis defines the measurement method of body segments that is mostly treated as five cylinders as in Figure 1 [5], and was introduced to overcome the disagreement between trunk resistance to upper limbs ratio and trunk resistance to lower limbs ratio of 0.72 and 0.66 respectively [52]; Earthman et al. stated that the trunk represents 50% of the body mass [55]. Kyle et al. pointed out that total bioimpedance measurement assesses mainly the upper and lower limb compartments, and shows some limitation to predict water compartments of the trunk [13].

Measurement of segmental bioimpedance can be achieved through four types of protocols. The first approach, as suggested by Scheltinga et al. [56], uses dual current injection electrodes on the proximal area of the right forearm and lower leg, and quad voltage electrodes placed on the right proximal forearm, shoulder, upper thigh and lower leg (Figure 4a). The second approach is suggested by Zhu et al. [57], through the sum of segments technique, that uses dual current injection electrodes on the right wrist and foot, and quad voltage electrodes placed on the right wrist, shoulder, upper iliac spine and foot (Figure 4b). A third approach was presented by Organ et al. [58], who suggested the use of dual current injection electrodes on the right wrist and foot, and quad voltage electrodes, two placed on the right wrist and foot, and two on the left wrist and foot (Figure 4c). The fourth approach as suggested by Jaffrin et al. [16,59,60], is through the use of quad current injection electrodes located on the right and left wrist and foot, and quad voltage electrodes located at the same place (Figure 4d).

Figure 4.

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Segmental bioimpedance analysis techniques, (a) right side dual current and quad voltage electrodes, (b) right side dual current and quad voltage electrodes, (c) double sides dual current and quad voltage electrodes and (d) double sides quad current and quad voltage electrodes.

Limitations of whole body bioimpedance measurement in eval‎uating body segment compartments have given rise to the demand for segment localized bioimpedance analysis applications. Scharfetter et al. [40], reported that using segmental (across the waist) localized bioimpedance analysis can significantly estimate abdominal fat with a correlation coefficient of R2 = 0.99; furthermore Seward et al. [61], introduced localized bioimpedance analysis as a trending diagnostic tool for neuromuscular disorders. The study was applied on 25 neuromuscular patients and 45 normal subjects for control.

Studies report that the segmental bioimpedance analysis method shows some limitations in the estimation of FFM [62,63], with estimation power not significantly different from whole body bioimpedance method [44]. However, Kyle et al. [13] concluded that enhancement can be achieved through applying the MF-BIA method and further studies on electrode types and allocation.

2.6. Alternative Bioimpedance Analysis Method

Bioimpedance analysis, as an independent method for the assessment of the human health status from absolute bioimpedance measurements, has triggered a new path of data analysis and interpretation. The bioimpedance vector analysis method (BIVA) is a novel approach established essentially by Piccoli et al. [64,65] to estimate the hydration status using height indexed resistance and reactance data (R-Xc graph) from bioimpedance measurements. Using 8,022 normal subjects (3796 female and 4226 male) Piccoli et al. [66] formulated 50%, 75%, and 95% tolerance ellipses that determine increasing and decreasing body mass if the minor vector falls in the left and right half of the 50% ellipse, along with increasing and decreasing hydration ratio if the major vector falls in the lower and upper half of the 50% ellipse (Figure 5).

Figure 5.

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Bioimpedance vector analysis (BIVA) and tolerance ellipses.

Eval‎uation study of the BIVA method by Cox-Reijven et al. [67], on 70 diseased subjects with gastrointestinal disorders, conclude the high specificity and low sensitivity of BIVA method in classifying patients with extraordinarily rates of body fluids. Low values (Xc/H < 27.7 O/m and R/H < 563.6 O/m) in the BIVA method can be considered as predictors of severity among diseased children, as shown in a study conducted on 332 precarious pediatric patients with multiple organ dysfunction (MODS), acute respiratory distress syndrome (ARDS) and acute lung injury (ALI) [68].

In [69] the BIVA method successfully monitored rapid increases in ECF during short term recovery (3 weeks) and a dramatic increase in BCM during long term recovery (3 months) among 47% of 57 diseased women with anorexia nervosa [5].

The BIVA method is also considered as a valid tool for the estimation of dry weight in 24 haemodialysis patients' with reference to the Bilbrey Index based on different allocation of values before and after obtrusion [70].

Kyle et al. reported that the BIVA method is affected by differences in biological factors and measurement artifacts [5]. Ward and Heithmann state that BIVA is affected by body size and influenced by the cross-sectional area of the body [71].

A specific BIVA method has been proposed by Marini et al. [72] to neutralize the bias due to body size. The specific BIVA method used a resistivity-reactivity graph that is constructed using information and results collected from multiplication of resistance and reactance by ratio of cross section area and length (L/A) from Ohm's law (Equation (1)). The cross section area (A) and length (L) were estimated as follows: A = (0.45(arm area) + 0.45(calf area) + 0.10(waist area)) in square meter [73,74], where segment area = c2/4π and (c) is the circumference in meter of the arm, waist and calf, respectively; L = 1.1 (Ht), where Ht is body height in meters.

Another alternative method for analysis is real time processing of bioimpedance data which is currently introduced as a key feature for body health monitoring applications. A logarithmic analysis carried out between 0.01 and 10 Hz with five frequencies needs 276 s to be completed, this includes the calculation time [75]. Sanchez et al. [76] stated that real time processing, accuracy and the ability of data retrieval‎ and throughput of a BIS system were the most important features to be applied in health monitoring systems, and Sanchez et al. [77] introduced a local polynomial based method for impedance-frequency-response estimation. Comparison studies between four different multi-sine periodic broadband excitations broadband for EIS measurements in term of accuracy and speed in frequency and time domain concluded that multi-sine and discrete interval binary sequences (DIBS) enhance SNRZ and have better accuracy than chirp and maximum length binary sequences (MLBS) [75].

Use of multi-sine excitation signals in bioimpedance measurements that is proposed in [78,79] helped increase the accuracy of the measured bioimpedance parameters. It has been validated using a set of optimal multi-sine measurements on 2R-1C equivalent electrical circuits, then applied on healthy myocardium tissue. The multi-sine excitation method was introduced as a parametric-in-time identification method for electrical bioimpedance measurements with inclusion of harmonic impedance spectra (HIS). HIS directly identified from noisy current and voltage myocardium measurements at the multi-sine measurement frequencies to express periodic changes of impedance, rather than the commonly used method that assumed the measurement changing over time [80].

3. Body Composition Prediction Using Bioimpedance Analysis

Body composition assessment is considered a key factor for the eval‎uation of general health status of humans. Several methods use different assumptions to estimate body composition based on the number of compartments. This review considers that the human body is composed of two main compartments, FM and body lean mass or FFM. FFM is composed of bone minerals and body cell mass (BCM) that includes skeletal muscle mass (SMM). BCM contains proteins and TBW that represents 73% of lean mass in normal hydrated subjects. TBW is composed of ICF and ECF as illustrated in Figure 1. In this section, several predictive equations for both lean and fat mass, in addition to body fluids, will be discussed.

3.1. Fat Mass (FM) and Fat Free Mass (FFM)

FM and FFM estimations are considered one of the main objectives of body composition assessment techniques. Variations in FM among the reference population are due to several factors, but are believed to follow aging factors in addition to gradual changes in lifestyle [81].

Anthropometric and skin fold thickness measurements are traditional, simple and inexpensive methods for body fat estimation to assess the size of specific subcutaneous fat depots [82] compared with other methods such as underwater weighing, dilution method and dual-energy x-ray absorptiometry [DXA] that requires a trained practitioner to perform it.

Bioimpedance analysis has been shown in recent studies to be more precise for determining lean or fat mass in humans [83]. In comparison with BMI, anthropometric and skin fold methods, BIA offers trustable results in the estimation of fatness across human tissues [84]. Several studies conducted to establish reference values for FFM are based on bioimpedance measurements.

Kyle et al. [13] developed a single Equation (12) for the prediction of FFM, using 343 normal subjects aged from 22 to 94 years old, with body mass indexes between 17.0 and 33.8 kg/m2 in reference to DXA method:

𝐹𝐹𝑀=−4.104+0.518⁢ℎ⁡𝑡2/𝑅50+0.231⁢𝑤⁢𝑡+0.130⁢𝑋𝑐,50)+4.229⁢𝑠𝑒𝑥𝑆𝑒𝑥{1,𝑀𝑎𝑙𝑒0,𝐹𝑒𝑚𝑎𝑙𝑒

(12)

where (Ht) is body height, (R50) and (XC, 50) is resistance and reactance at 50 KHz, and (Wt) is body weight. The developed equation achieved a correlation coefficient (R) that is equal to 0.986, standard error of the estimate (SEE) is equal to 1.72 kg and technical error is 1.74 kg.

In [81,85], FFM was assessed in a population of 5,225 white subjects aged from 15 to 98 years old using bioimpedance measurements and it was concluded that mean FFM was 8.9 kg or 14.8% lower in men older than 85 years than in men 35 to 44 years old and 6.2 kg or 14.3% lower in women older than 85 years than in women 45 to 54 years old.

Sun et al. [86], used a multi-component model based on densitometry, isotope dilution, and dual-energy X-ray absorptiometry to build Equations (13) and (14) for FFM estimation:

𝐹𝐹𝑀𝑚𝑎𝑙𝑒=−10.68+0.65⁢ℎ⁡𝑡2/𝑅50+0.26⁢𝑤⁢𝑡+0.02⁢𝑅50

(13)

𝐹𝐹𝑀𝑓𝑒𝑚𝑎𝑙𝑒=−9.53+0.69⁢ℎ⁡𝑡2/𝑅50+0.17⁢𝑤⁢𝑡+0.02⁢𝑅50

(14)

The mean FFM prediction equations achieved a correlation coefficient R2 = 0.90 and 0.83 and root mean square errors of 3.9 and 2.9 kg for males and females, respectively.

Deurenberg et al. [87], used densitometry, anthropometry and bioelectrical impedance to formulate FFM prediction Equation (15) using 661 normal adult subjects aged from 7 to 83 years old:

𝐹𝐹𝑀=−12.44+0.34⁢𝐻⁡𝑡2/𝑅50+0.1534⁢𝐻⁡𝑡+0.273⁢𝑊⁢𝑡−0.127𝐴𝑔𝑒+4.56⁢𝑆𝑒𝑥𝑆𝑒𝑥{1,𝑀𝑎𝑙𝑒0,𝐹𝑒𝑚𝑎𝑙𝑒

(15)

The FFM prediction equations achieved a correlation coefficient R2 = 0.93 and standard estimation error (SEE) = 2.63 kg.

Pichard et al. [88], assessed FFM and FM in a 3,393 white subject population aged from 15 to 64 years old using bioimpedance measurements and performed a comparison of %FM as determined by BIA with %FM determined by calculations using BMI developed by Deurenberg et al. [89], and concluded that the mean FFM ranged of 59.1–61.0 kg for men and 43.3–44.1 kg for women which is 38% greater in men.

Heitmann [90] compared three body composition methods (BMI, skin folds and BIA) using 139 healthy subjects aged from 35 to 65 years old:

𝐹𝑀=14.94−0.079⁢𝐻⁡𝑡2/𝑅50+0.818⁢𝑤⁢𝑡−0.231⁢ℎ⁡𝑡−0.064𝑠𝑒𝑥𝑤𝑡+0.077⁢𝐴𝑔𝑒

(16)

The multiple regression Equation (16) for impedance had a higher correlation coefficient (R2 = 0.89) and lower standard estimation error (SEE = 3.32 kg) than the multiple regression equations for skin fold (R2 = 0.81, SEE = 3.91 kg) or body mass index (R2 = 0.85, SEE = 3.94 kg).

Heitmann [88] assessed FFM and FM in 2987 out of a 3608 subject Danish population aged from 35 to 65 years old. The obtained data, which are estimated from measurements of electrical impedance, concluded that men have a FM of 4.5 kg, an increase by 30%, when compared to women that have a 6.9 kg increase of 36% for eval‎uated sample.

Recently, Pichler et al. [91] assessed FM in 116 subjects (32 healthy subjects and 84 patients) and concluded that the following prediction equation overestimated FM by 6.55 ± 3.86 kg:

𝐹⁡𝑀𝑀𝑎𝑙𝑒=−18.42+0.60⁢𝑊⁢𝑡−0.57⁢𝐻⁡𝑡2𝑅𝑡𝑏𝑤+0.62⁢𝐻⁡𝑡2𝑅𝑒𝑐𝑓

(17)

𝐹⁡𝑀𝐹𝑒𝑚𝑎𝑙𝑒=−9.81+0.65⁢𝑊⁢𝑡−0.66⁢𝐻⁡𝑡2𝑅𝑡𝑏𝑤+0.65⁢𝐻⁡𝑡2𝑅𝑒𝑐𝑓

(18)

where Recf and Rtbw represents resistance of extracellular fluids and total body water extracted using the Cole module [26]. In conclusion, all studies state that the men have higher estimated FM as compared to women. Moreover, FFM for both genders decreases progressively with increasing age [81,88].

3.2. Body Fluids

Body fluid is the total volume of fluids inside a human body that represents the majority of the FFM volume percentage. TBW includes the fluids inside the cellular mass that is known as ICF; and the fluid located outside the cell body which is composed of plasma and interstitial fluid which is known as ECF. ECF and ICF fluids that are incorporated under TBW, contain several ion types with different concentrations, however the main ions in ECF are Na+ and Cl−, and for ICF are K+ and PO−4 [92].

Body fluids estimation using bioimpedance measurements are based on the inversely proportional between body resistance and the total amount of body water [93]. There are varieties of methods for estimating body fluid volumes based on bioimpedance analysis approach.

Sun et al. [86] developed prediction Equations (19) and (20) of the TBW reference to dilution method using SF-BIA from a multi-ethnic pool of 1830 people aged from 12 to 94 years old:

𝑇𝐵𝑊𝑚𝑎𝑙𝑒=1.2+0.45⁢𝐻⁡𝑡2/𝑅50+0.18⁢𝑊⁢𝑡

(19)

𝑇𝐵𝑊𝑓𝑒𝑚𝑎𝑙𝑒=3.75+0.45⁢𝐻⁡𝑡2/𝑅50+0.11⁢𝑊⁢𝑡

(20)

The developed equation achieved a correlation coefficient (R2) and mean square error equal to 0.84 and 3.8 L in men, and 0.79 and 2.6 L in women.

For ECF and ICF estimation using SF-BIA, a few studies performed were based on measurement of bioimpedance in 50 KHz frequency, Sergi et al. [94], predict ECF using two frequencies (1 and 50 KHz):

𝐸𝐶𝐹50⁢𝐾𝐻𝑧=−5.22+0.20⁢𝐻⁡𝑡2/𝑅50+0.005⁢𝐻⁡𝑡2/𝑋⁢𝑐50+0.08⁢𝑊⁢𝑡+1.9𝐻𝑒𝑎𝑙𝑡ℎ+1.86⁢𝑆𝑒𝑥

(21)

𝐸𝐶𝐹50⁢𝐾𝐻𝑧=−7.24+0.34⁢𝐻⁡𝑡2/𝑅1+0.06⁢𝑊⁢𝑡+2.63𝐻𝑒𝑎𝑙𝑡ℎ+2.57⁢𝑆𝑒𝑥𝑆𝑒𝑥{1,𝑀𝑎𝑙𝑒0,𝐹𝑒𝑚𝑎𝑙𝑒;𝐻𝑒𝑎𝑙𝑡ℎ{1,𝐻𝑒𝑎𝑙𝑡ℎ𝑦2,𝐷𝑖𝑠𝑒𝑎𝑠𝑒𝑑

(22)

After measurements performed using bioimpedance and bromide dilution methods on 40 subjects (19 males and 21 females) aged 21–81 years, of which 22 were healthy subjects, 12 were affected by chronic heart failure and 6 by chronic renal failure, the best estimation results at 1 KHz achieved a correlation coefficient (R2) and standard estimation error equal to 0.89 and 1.7 L.

Due to incomplete conduction of the intracellular fluid at 50 kHz [2], MF-BIA was proposed to increase accuracy of estimation of TBW, ECF and ICF. Deurenberg et al. [95] used MF-BIA (1, 5, 50, 100 KHz) to predict TBW using Z100KHz and Z50KHz; and ECF using Z1KHz and Z5KHz among 139 normal adult subjects with reference to deuterium oxide dilution and bromide dilution:

𝑇𝐵𝑊100⁢𝐾𝐻𝑧=6.69+0.34573⁢𝐻⁡𝑡2/𝑍100+0.17065⁢𝑊⁢𝑡−0.11𝐴𝑔𝑒+2.66⁢𝑆𝑒𝑥

(23)

𝑇𝐵𝑊50⁢𝐾𝐻𝑧=6.53+0.36740⁢𝐻⁡𝑡2/𝑍100+0.17531⁢𝑊⁢𝑡−0.11𝐴𝑔𝑒+2.83⁢𝑆𝑒𝑥𝑠𝑒𝑥{1,𝑀𝑎𝑙𝑒0,𝐹𝑒𝑚𝑎𝑙𝑒

(24)

The prediction equation of TBW achieved a correlation coefficient (R2) and standard error of estimate (SEE) equal to 0.95 and 1.73 L using Z100KHz, and 0.95 and 1.74 L using Z50KHz:

𝐸𝐶𝐹1⁢𝐾𝐻𝑧=2.30+0.19528⁢𝐻⁡𝑡2/𝑍1+0.06987⁢𝑊⁢𝑡−0.02⁢𝐴𝑔𝑒

(25)

𝐸𝐶𝐹5⁢𝐾𝐻𝑧=2.53+0.18903⁢𝐻⁡𝑡2/𝑍5+0.06753⁢𝑊⁢𝑡−0.02⁢𝐴𝑔𝑒

(26)

The prediction equation of ECF achieved a correlation coefficient (R2) and standard error of estimate (SEE) equal to 0.87 and 0.98 L using Z1KHz, and 0.86 and 1.02 L using Z5KHz.

Prediction of body fluids using the BIS method in three steps involves firstly determination using the values of Re from R0 and Rinf, secondly, inclusion of the body shape factor Kb due to the variation of body segments, and thirdly, inclusion of apparent resistivity ρa instead of the general resistivity ρ as stated by Hanai in mixture theory [18]:

𝜌𝑎=𝜌(1−𝑐)32

(27)

where (c) is volume fraction of non-conducting tissue. Based on Hanai's mixture method [18], tissue resistance (R) is measured based on conductive tissue, so it should exclude non-conducting tissue. Thus, by substituting Equation (27) in Equation (11), the apparent resistance (Ra) can be calculated using the following Equation (28):

𝑅𝑎=𝐾𝑏⁢𝜌⁢𝐻⁡𝑡2𝑉𝑏⁢(1−𝑐)3/2

(28)

At low frequencies the current will pass through extracellular fluids only without intracellular fluid due to the high capacitance of cell membranes [96]. In that case the conducting volume is equal to the ratio between ECF volume (Vecf) and TBW volume (Vb). The volume fraction of non-conducting tissues at low frequencies calculated as in Equation (29):

𝑐=1−𝑉𝑒𝑐𝑓𝑉𝑏

(29)

Based on the mixture theory [18], apparent resistivity (ρa) at low frequency represents the extracellular fluid resistivity (ρAecf), thus the resistance of ECF (Recf) can be recalculated in Equation (31), by substituting Equation (29) in Equation (28) and including the outcome of apparent resistivity (ρaecf) from Equation (30):

𝜌𝑎𝑒𝑐𝑓=𝜌𝑒𝑐𝑓⁢(𝑉𝑏𝑉𝑒𝑐𝑓)3/2

(30)

𝑅𝑒𝑐𝑓=𝐾𝑏⁢𝜌𝑒𝑐𝑓⁢𝑉𝑏1/2𝑉𝑒𝑐𝑓3/2

(31)

Hanai [18], calculated ρecf to be equal to 40.3 Ω ·cm for men and 42.3 Ω ·cm for women, which is close to that achieved by saline, and is about 40 Ω ·cm t for the ECF composed of plasma and interstitial water [49].

To reform the equation to eval‎uate the variance in ECF volume (Vecf) caused by changes in estimated ECF resistance (Recf), that is achieved by replacing body volume (Vb), that is equal to the ratio between body weight (Wt) in Kg and body density (Db) in Kg/L from Equation (32) in Equation (33):

𝑉𝑏=𝑊⁢𝑡𝐷𝑏

(32)

𝑅𝑒𝑐𝑓=𝐾𝑏⁢𝜌𝑒𝑐𝑓⁢(𝑊⁢𝑡𝐷𝑏)1/2𝑉𝑒𝑐𝑓3/2

(33)

Body factor (Kb), extracellular fluid resistivity (ρaecf) and body density (Db) are constant values that can be included in one factor defined as extracellular fluid factor (Ke) as in Equation (34), and for extracellular fluid volume (Vecf) as in Equation (35):

𝐾𝑒=10−2⁢(𝐾𝑏⁢𝜌𝑒𝑐𝑓𝐷12𝑏)2/3

(34)

𝑉𝑒𝑐𝑓=𝐾𝑒⁢(𝐻⁡𝑡2⁢(𝑊⁢𝑡)12𝑅𝑒𝑐𝑓)2/3

(35)

Van Loan et al. [43], calculated Ke using the bromide dilution method to be equal 0.306 for men and 0.316 for women; and the ratio between ρicf and ρecf to be equal to 3.82 for men and 3.40 for women. De Lorenzo et al. [10] calculated Ke to be equal to 0.229 in women; and ρecf to be equal to 40.5 Ω ·cm and 39.0 Ω ·cm for men and women, respectively; and the ratio between ρicf and ρecf to be equal to 6.76 for men and 6.79 for women.

Ellis and Wong [30], analyzed the BIS method as introduced by Van Loan et al. [43], with reference to the H2O and Br dilution technique in 469 multi-ethnic healthy subjects. The study suggested that the ratio between ρicf and ρecf is equal to 3.032 for men and 2.694 for women, due to underestimation of TBW caused by misprediction of ICF measurements. Biasing factors and different regression module approaches caused slight differences in the ratios obtained by these researchers [30].

Moissl et al. [97], suggested a body composition spectroscopy method through recalculating Kecf , using different assumptions through inclusion of body mass index (BMI) and taking the module of non-conducting tissue factor (c) in Equation (14) as a valid assumption, as in Equation (36), and then determining the (Vecf) using the same equation as Equation (20):

𝐾𝑒𝑐𝑓=(𝑎𝐵𝑀𝐼+𝑏)

(36)

From [97], (a) and (b) were calculated to be equal to 0.188 and 0.2883 based on measurements using the Br dilution method as a reference method on dialyzed patients and 120 healthy subjects. At high frequencies, the current will pass through the whole TBW which is composed of ECF and ICF [96], so the conducting volume is equal to the ratio between TBW and total body volume.

Jaffrin et al. [31] suggested calculating the TBW directly from Rinf using the same assumption of mixture theory [96], and assuming uniformity of water compartments inside human body. Thus, using the same assumption as in Equation (29), the volume fraction of non-conducting tissue (c) at high frequencies can be calculated using Equation (37):

𝑐=1−𝑉𝑏𝑉𝑡𝑏𝑤

(37)

To determine the apparent resistivity of total body water (ρa_tbw) from actual total body water resistivity (ρtbw), the parameters in (c) from Equation (37), was included into Equation (38):

𝜌𝑎_𝑡𝑏𝑤=𝜌𝑡𝑏𝑤⁢(𝑉𝑏𝑉𝑡𝑏𝑤)3/2

(38)

By replacing the actual resistivity by apparent resistivity for total body water in Equation (11), and restoring the value of (Vb) from Equation (32), Equation (40) to determine the total body water factor (Ktbw) and total body water volume (Vtbw) is recalculated by using Equation (39):

𝐾𝑡𝑏𝑤=(𝐾𝑏⁢𝜌𝑡𝑏𝑤𝐷𝑏1/2)2/3

(39)

𝑉𝑡𝑏𝑤=𝑘𝑡𝑏𝑤⁢(𝐻⁡𝑡2⁢𝑊⁢𝑡12𝑅𝑡𝑏𝑤)2/3

(40)

Considering that total body water is equal to the accumulation of ECF and ICF, Jaffrin et al. [31] calculated ρtbw to be equal to 104.3 Ω ·cm in men and 100.5 Ω ·cm. A validation study conducted in 28 dialysed patients [31], concluded that ρtbw was equal to 108.1 Ω·cm in men and 100.2 Ω·cm, which predicted 91% of mean water loss when compared with 39% for Cole method [43], but overestimated TBW compared to the original BIS method in 21 healthy subjects with the same ρtbw and hydration rate values.

For ICF prediction using a BIS method, Matthie et al. [32] introduced a second generation mixture theory to overcome the limitations of the first generation in predicting intracellular fluid volume (Vicf) using a new assumption for TBW resistivity (ρtbw), as in Equation (32):

𝜌𝑡𝑏𝑤=𝜌𝑖𝑐𝑓−(𝜌𝑖𝑐𝑓−𝜌𝑒𝑐𝑓)⁢(𝑅𝑡𝑏𝑤𝑅𝑒𝑐𝑓)23

(41)

In the second version of mixture theory, total body water volume is considered to be equal to the summation of ECF and ICF, for ECF estimation, the relation in Equation (35) is considered as a valid method, and for ICF estimation, the method uses Equation (42); note that the ratio (Rtbw/Recf) is opposite and proportional to (Vtbw/Vecf):

𝑉𝑖𝑐𝑓=𝑉𝑒𝑐𝑓.([𝜌𝑡𝑏𝑤.𝑅𝑒𝑐𝑓𝜌𝑒𝑐𝑓.𝑅𝑡𝑏𝑤]2/3−1)

(42)

Moissl et al. [97] calculated ρicf to be equal to 273.9 Ω·cm and ρecf = 40.5 Ω·cm in men and 264.9 Ω·cm and 39.0 Ω·cm, respectively in women. De Lorenzo et al. [10] suggest the formula in Equation (34) to determine intracellular volume (Vicf):

(1+𝑉𝑖𝑐𝑓𝑉𝑒𝑐𝑓)5/2=𝑅𝑖𝑐𝑓+𝑅𝑒𝑐𝑓𝑅𝑖𝑐𝑓⁢(1+𝜌𝑖𝑐𝑓⁢𝑉𝑖𝑐𝑓𝜌𝑒𝑐𝑓⁢𝑉𝑒𝑐𝑓)

(43)

Jaffrin and Morel [21] claim that the prediction of ECF by Hanai [18] mixture theory is valid and direct, however the ICF prediction by De Lorenzo et al. [10], who state that the determination of Ri is less accurate than for Re in parallel module because it sums up the errors on Re and Rinf, is not.

Moissl et al. [97] introduced a different method for calculation of intracellular fluid volume (Vicf), taking into consideration that the non-conducting tissue factor (c) is as given in Equation (44):

𝑐=1−𝑉𝑖𝑐𝑓𝑉𝑏

(44)

Then the recalculated intracellular fluid factor (Kicf) and intracellular fluid volume (Vicf) are added as in Equations (45) and (46), respectively, and it is concluded that total body water factor (Ktbw) and total body water volume (Vtbw) is equal to the summation of ECF and ICF volumes as in Equation (47) and recalculated (Vtbw) using different assumption of (Ktbw) and (ρtbw) from Jaffrin et al. [31], and Matthie et al. [32], as given in Equations (48) and (49):

𝐾𝑖𝑐𝑓=(𝑐𝐵𝑀𝐼+𝑑)

(45)

𝑉𝑖𝑐𝑓=𝐾𝑖𝑐𝑓⁢(𝐻⁡𝑡2⁢𝑊⁢𝑡1/2𝑅𝑖𝑐𝑓)23

(46)

𝑉𝑡𝑏𝑤=(𝑉𝑒𝑓+𝑉𝑖𝑓)=(𝐻⁡𝑡2⁢𝑊⁢𝑡1/2)13⁢⎛⎜⎝⎛⎜⎝𝑘𝑒𝑓𝑅23𝑒𝑐𝑓⎞⎟⎠+⎛⎜⎝𝑘𝑖𝑓𝑅23𝑖𝑐𝑓⎞⎟⎠⎞⎟⎠

(47)

𝐾𝑡𝑏𝑤=𝐾𝑒𝑐𝑓⁢(𝑅𝑡𝑏𝑤𝑅𝑒𝑐𝑓)2/3+𝐾𝑖𝑐𝑓⁢(𝑅𝑡𝑏𝑤𝑅𝑖𝑐𝑓)2/3=(𝐾𝑏⁢𝜌𝑡𝑏𝑤𝐷𝑏1/2)2/3

(48)

𝜌𝑡𝑏𝑤=(𝐷𝑏1/2𝐾𝑏)⁢[𝐾𝑒𝑐𝑓⁢(𝑅𝑡𝑏𝑤𝑅𝑒𝑐𝑓)2/3+𝐾𝑖𝑐𝑓⁢(𝑅𝑡𝑏𝑤𝑅𝑖𝑐𝑓)2/3]

(49)

where (c) and (d) are calculated to be equal to 5.8758 and 0.4194 in [97], when using the 40K isotope [98] as a reference method on dialyzed patients and 120 healthy subjects.

Fenech and Jaffrin [2] state that ECF prediction using segmental bioimpedance analysis in supine position (0.79 liter) is less than Watson anthropomorphic method [3] (1.12 liter) and for ICF is reduced by 3.4% for segmental bioimpedance and 3.8% for the Watson anthropomorphic method [3]:

𝑉𝑡𝑏𝑤,𝑀𝑎𝑙𝑒=2.447−0.09156𝐴𝑔𝑒+0.1074⁢𝐻⁡𝑡+0.3362𝑊⁢𝑡

(50)

Pichler et al. [91] examined the BIS method using an Impedimed device (SFB7) in TBW, ECF and FFM with reference to the deuterium space method, sodium bromide space method and DXA method, respectively. The study was applied on 32 healthy subjects and 84 patients with different types of diseases (congestive heart failure, coronary heart disease, essential hypertension, atherosclerosis, kidney disease, chronic renal failure, gastrointestinal diseases, type II diabetes, morbid obesity, osteoporosis, cancer, chronic polyarthritis and anorexia nervosa):

𝑉𝑡𝑏𝑤_𝑀𝑎𝑙𝑒=8.75+0.23⁢𝑊⁢𝑡+0.21⁢𝐻⁡𝑡2𝑅𝑡𝑏𝑤

(51)

𝑉𝑡𝑏𝑤_𝐹𝑒𝑚𝑎𝑙𝑒=5.94+0.19⁢𝑊⁢𝑡+0.24⁢𝐻⁡𝑡2𝑅𝑡𝑏𝑤

(52)

𝑉𝑒𝑐𝑓_𝑀𝑎𝑙𝑒=0.11+0.11⁢𝑊⁢𝑡+0.24⁢𝐻⁡𝑡2𝑅𝑒𝑐𝑓

(53)

𝑉𝑒𝑐𝑓_𝐹𝑒𝑚𝑎𝑙𝑒=1.24+0.09⁢𝑊⁢𝑡+0.28⁢𝐻⁡𝑡2𝑅𝑒𝑐𝑓

(54)

Pichler's equations for TBW achieved a correlation coefficient 0.91 and 0.89 for men and women, respectively, as in Equations (51) and (52). For ECF it achieved 0.87 and 0.89 for men and women, respectively, as in Equations (53) and (54) [91]. Hanai mixture equations [18], when applied in SFB7 give ECF measurements higher than the sodium bromide space method by mean ± SD (0.93 ± 2.62 Liter) however it is noted that the Hanai mixture equations applied in SFB7 detect ECF excess in 9 patients, and TBW measurements higher than the deuterium space method by mean ± SD (3.82 ± 3.37 Liter), and FFM measurements lower than the DXA method by mean ± SD (6.55 ± 3.86 kg).

4. Bioimpedance Measurement Biasing Factors4.1. Anthropometric Measurements

Anthropometric measurements such as weight, height, skin fold thickness, lengths, diameters and circumferences that involves mathematical modules are the main contributors in the estimation of body compartments [5,99].

Bioimpedance parameters only without body dimension measurements are considered poor estimators for body composition [91,100]. Diaz et al. [101] concluded that in FM and FFM prediction, resistance and capacitance measurements contribute by 0%–20%. In contrast, the percentages increase to 11%–53% after height inclusion, and 22%–68% after inclusion of Ht2/R ratio.

Ward et al. [102] presented a validation study to predict BCM and ECF as a portion of TBW without measuring height and using BIA device, the Soft Tissue Analyzer STATM (Akern Sri, Florence, Italy) with a correlation coefficient referenced to the total body potassium counting method is equal to 0.91, 0.82 and 0.89, and a standard estimation error equal of 5.6 kg, 6.3 kg and 1.3 kg for FFM, BCM and ECF, respectively.

4.2. Gender

Variations in body composition between male and female were proven in several studies [103]. In body composition prediction, methods based on bioimpedance analysis, and most equations tend to include gender as one of the main determining factors for body compartment assessment [13,86,87].

FFM or lean mass studies show that males have greater FFM than females with different ranges. Kyle et al. [81] state that mean FFM for male is 8.9 kg and 6.2 kg for female and fat mass index FMI increases based on age, in females from 5.6 to 9.4 and from 3.7 to 7.4 in males. In a recent study [104] on 1649 healthy children-adults (6–18 years) and 925 adult-elders (19–92 years) using BIA and DXA it was concluded that for all age ranges, males have less fat mass and more fat free mass than females.

TBW averaged 73.2% of fat free mass in the healthy population; however several studies show that males have less TBW than females [11]. Sun et al. [86], stated that in a mixed ethnic groups prediction equation, TBW volume for males start from 1.2 L compared with 3.75 L for females. Jaffrin et al. [31] state that determined TBW resistivity (ρ) is on average 104.3 ± 7.9 Ω·cm for men and 100.5 ± 7.8 Ω·cm for women. The values are smaller in men are due to their larger limb cross section.

Due to the different body composition between males and females, gender considerations have a strong impact in estimating body compartments.

4.3. Age

Aging is defined as a multi-factor changing in the physical and biological activities of the human body that leads to differences in body composition among age groups. When the human body becomes older it leads to a gradual increase in fat mass and spontaneous decrease in lean mass. Fat free mass to fat mass ratio increases gradually in response to increase of age, and a noticeable increment in average weight is seen among the elder population compared with adults associated with increment in fat mass [81]. In some studies [58], the general body composition prediction equations were unsatisfactory in elderly men over 75 years of age, especially in TBW estimation.

Several studies were conducted using the BIA method on children [68,105] adults [13], and elders [106,107]. In children, the BIA method using the Deurenberg equation [87], underestimates body fat as determined by DXA. It however achieved a better correlation than the skin fold method [108]. Muscle mass loss among the elderly reduces the fat free mass at a certain age, followed by decreases in total body water and bone mass [109]. Marja et al. [107] reported that in 75-year-old Swedes, average fat free mass index was 15.6 and 18.3; and body fat index was 11.0 and 8.6 for women and men, respectively, compared to the DXA method.

4.4. Ethnic Groups

Body composition varies among different races and ethnic groups due to the environment, nutrition factors, culture and anthropometric measurements that include body conformation [110]. There is also difference in limb length [111], body structure [112], body size [89] and that lead to variation in body fat percentages among different ethnic groups which may lead to prediction errors (3%) [111].

The majority of bioimpedance measurement studies have been done on Caucasian subjects [5], Kotler et al. [113] and Sun et al. [86] have included African American and Hispanic subjects in their studies. Kim et al. assessed the segmental lean mass among Koreans [106], Schulz et al. assessed the fat free mass among Germans and compared it to the American and Swiss population [114]. Siváková et al. studied the clinical applications of BIVA on Slovaks [115]. Nigam et al. had performed a comparative study among two different Indian races [116], whereas Saragat et al. obtained specific BIVA reference values for the Italian healthy elderly population in order to construct the specific tolerance ellipses to be used for reference purposes for assessing body composition in gerontological practice and for epidemiological purposes [117]. Validation of bioimpedance measurements among different ethnicities is thus needed due to differences in body composition among certain populations.

4.5. Measurements Protocols and Posture

Simplicity and the economic acceptance of bioimpedance analysis method for body composition estimation have increased the need to unify the protocols and procedures of bioimpedance measurements in order to retrieve robust data.

For the foot to ankle measurement method, bioimpedance measurements performed in a supine position with abduction of the upper limbs to 30 degrees and lower limbs to 45 degrees for 5 to 10 min. studies show that when the posture changes from a standing to a supine body position, the ECV decreased in the arms by 2.51% and legs by 3.02%, but increased in the trunk by 3.2% [118]. Fasting for at least 8 hours and bladder voiding before measurements are recommended as consumption of food and beverages may decrease impedance by 4–15 O over a 2–4 h period after meals and that causes an error (<3%) [84,119,120]. Body anthropometric measurements should be retrieved prior of the test and for scale or foot to foot bioimpedance analyzer weight retrieved automatically [1].

Electrodes should be placed on the pre-cleaned metacarpal and metatarsal phalangeal joints with a distance in between of at least 5 cm without skin lesions at the location of the electrodes. In some studies skin temperature should be counted [84,120]. Subjects under test should not perform any exercise activities before measurements that could lead to errors in assessed resistance and reactance equal to 3% and 8% respectively [121]. Roos et al. concluded that the error in total body water prediction range from 1 to 1.5 L figured out after laying at rest for one hour [122].

4.6. Electrode Shape and Measurement Error

In bioimpedance analysis, the geometrical structure of electrode has a strong impact on elementary data retrieved during the measurement process. In bioimpedance analysis electrodes are defined as isoelectric materials with a negligible voltage drop along the connectors. The minimum numbers of electrodes required to perform the bioimpedance measurements are two, one for current injection with the assumption of zero potential difference and the other for collecting the voltage drop with a negligible current flow and is more affected by position.

The tetrapolar electrode approach become widely used for whole bioimpedance measurements because of the uniformity of current distribution compared to monopolar electrodes [6], and the usage of more than two potential collecting electrodes or octapolar electrode method were used for segmental bioimpedance studies to assess compartments in different body segments [73].

Ag-AgCl electrodes are now used in most bioimpedance measurements because it has a well-defined DC potential with electrolyte gel to minimize the gap impedance between skin and electrodes. Circular and rectangular electrode shapes with a contact area greater than 4 cm2 are the most commonly used shapes [1].

Buendía et al. investigated the impact of electrode discrepancy on BIS measurements and concluded that mismatched potential electrode causes 4% overestimated measurements in resistance at zero and infinite frequency because of an imbalanced electrical field distribution [123]. Shiffman [124] addressed the artifacts caused by inaccurate distance between electrodes in four electrode measurement methods performed on a 17.5 cm segment of the thigh area. That study reported that the values of resistance and reactance were four times larger when the current injecting electrodes were placed 2.5 cm from the sensing electrodes. Scharfetter et al. stated that capacitance between different body segments and earth, and capacitance between the signal ground of the device and earth cause a significant false dispersion in the measured impedance spectra at frequencies >500 kHz [125].

Errors in bioimpedance measurements are caused by many factors such as motion, miss-positioning, connector length and fabrication errors. Moreover, the diversity of the commercially available bioimpedance analyzers cause a wide range of fluctuations in measurements between the devices. Thus the calibration of the components inside a bioimpedance analyzer such as signal generator, sensing apparatus, scales of weight and height and electrical interference should be conducted to ensure the reliability of the bioimpedance analyzers [1].

5. Applications of Bioimpedance Analysis in Clinical Status Monitoring and Diagnosis of Diseases

Bioimpedance analysis in healthcare practice contributes to the estimation of body compartments to assess the regular change in nutrition status in in-patients and to monitor nutritional risk in out-patients [126]. Most of the body composition assessment methods like BMI techniques, skin fold method and underwater weight measurements is used to estimate fat mass and fat free mass, however bioimpedance analysis can estimate FM and FFM in addition to total and particular body fluids which is very helpful for disease prognosis [127]. The National Health and Nutrition Examination Survey program in United States included bioimpedance analysis in the third NHANES program between 1999 and 2004 to assess the health and nutritional status of adults and children because of a general frustration with the dependability of the skin fold thickness method to estimate FM and FFM, especially in subjects with higher amount of segmented fat [128].

Observation of body compartment fluctuations like fat free mass, fat mass and total body water from normal limits are considered as key factors to be used in bioimpedance analysis in healthcare applications. Abnormal loss in lean body mass and unbalanced shifts in body fluids are the most measured parameters to be used to assess the healthiness of the human body. Analysis of bioimpedance parameters has bern used in several studies to estimate and analyze the changes in disorders of different kind of diseases.

Norman et al. [70] stated that phase angle is an essential predictor of clinical status. Pichler et al. [91] stated that estimation of body fluids using BIS was slightly better than anthropometric methods among healthy and diseased.

Table 1 contains some of the applications of bioimpedance analysis in disease diagnosis that are organized according to the organ systems of human body, diseases or abnormalities diagnosed based on bioimpedance parameters, and comments on how these factors are applied to determine the health condition. Bioimpedance analysis is a common method used for estimating body composition among healthy and diseased subjects in research and clinical trials. This review has focused on the theoretical and the fundamentals of bioimpedance analysis. Thus it may have some limitations, where possible important studies on the applications of bioimpedance analysis in diagnostic of diseases and the related shifts in bioimpedance parameters may have been missed.

Table 1.

Applications of bioimpedance analysis in clinical status monitoring and diagnosis of diseases.

Organ SystemsDiseasesBIA ParametersRemarksAuthors

Pulmonary system	Lung cancer, stages IIIB and IV	R and Xc (BIVA)	Reactance components decrease in patients (phase angle <4.5). Clinical Study.	Toso et al., 2000 [129]
	Pulmonary edema monitoring	R (SFBIA)	Mean resistivity for left and right lung (1205 ± 163, 1200 ± 165 Ω·cm) and system reproducibility (2%). Research Study.	Zlochiver et al., 2007 [130]
Cardio-vascular system	Fluid accumulation after cardiac surgery.	Ht2/Z (MFBIA)	Significant increase in segmental trunk bioimpedance after surgery due to fluid accumulation. Clinical Study.	Bracco et al., 1998 [131]
Circulatory system	Volaemic status and hyponatraemia	TBW (SFBIA)	In elderly hyponatraemic patients, TBW assessment using BIA method was correlated with dilution of deuterium oxide (R = 0.68). Clinical Study.	Hoyle et al., 2011 [132]
	Hydration status and hyponatraemia in elderly	TBW (SFBIA)	Assessment of hydration status in elderly hyponatraemic patients using BIA method was more accurate than clinical procedures (Cohen's kappa coefficient = 0.52). Clinical Study.	Cumming et al., 2014 [133]
Renal system	Chronic hemodialysis	ECF (BIS)	ECF to weight ratio of hypertensive patient's increase from that of normal patients (24.29 ± 3.56% vs. 21.50 ± 2.38). Clinical Study.	Chen et al., 2002 [134]
	Dry weight in kidney failure.	ECF (BIS)	ECF/Wt is 0.239 and 0.214 L/kg for male and female healthy subjects. Clinical Study.	Chamney et al., 2002 [135]
	Hydration states monitoring in hemodialysis patients	Calf-BIS (BIS)	Normalized resistivity (μ = ρ /BMI) increased from 17.9 ± 3 to 19.1 ± 2.3 × 10−2 Ω3·Kg−1, and weight was reduced from 78.3 ± 28 to 77.1 ± 27 kg in Post-dialysis. Research Study.	Zhu et al., 2007 [136], 2008 [137]
	Dry weight assessment hemodialysis patients	Calf-BIS (BIS)	Dry weight assessed by cBIS underestimate left ventricular mass and blood pressure while antihypertensive medication remains unchanged. Clinical Study.	Seibert et al., 2013 [138]
	Body fluids estimation in hemodialysis patients	ECF, ICF and TBW (BIS)	Correlation between proposed equation corrected for BMI and the references (mean ± SD) was −0.4 ± 1.4 L for ECF, 0.2 ± 2.0 L for ICF and −0.2 ± 2.3 L for TBW. Clinical Study.	Moissl et al., 2006 [97]
	Dry weight assessment HD patients	R and Xc (BIVA)	BIVA method shows significant different in vectors in post dialysed patients. Clinical Study.	Atilano et al., 2012 [139]
Neural system	Alzheimer's disease	R and Xc (BIVA)	BCM decreased in patients for men, T2 (Hotelling's statistic) = 12.8 and for women, T2 = 34.9. Clinical Study.	Buffa et al., 2010 [140]
	Anorexia nervosa (eating disorder)	FM, FFM, TBW and ECF (BIS)	The BCM to Ht2 ratio was found to be significantly changed between diseased and controls subjects. Clinical Study.	Moreno et al., 2008 [141]
	Anorexia nervosa (eating disorder)	R and Xc (BIVA)	Gradually increasing in BCM and decreasing in ECF during treatments. Clinical Study.	Haas et al., 2012 [69]
Muscular system	Body composition changes monitoring during exercise training	FFM and FM (MFBIA)	BIA method underestimates FM (−3.42 kg) and overestimated FFM (3.18 kg); and undetected small shift in body composition due to exercise training. Clinical Study.	Sillanpää et al., 2013 [142]
Immunology system	Comparison between SFBIA and MFBIA in HIV patients	ECF and TBW (BIS)	Insignificant differences in TBW and ECF estimation using SFBIA, MFBIA and BIS methods. Clinical Study.	Paton et al., 1998 [143]
	Dengue haemorrhagic fever estimation in children	ECF and ICF (BIS)	(ECF/ICF) increase with increasing dengue virus infections severity in children. Clinical Study.	Libraty et al., 2002 [144]
	Cancer patients	TBW (SFBIA)	Change in TBW using BIA method (Ht2/R50) correlate with deuterium dilution in underweight and normal-weight cancer patients (R2 = 0.43 and SEE = 1.22 L). Clinical Study.	Simons et al., 1999 [145]
	Early diagnosis and risk analysis of dengue	R, C, φ and Xc (SFBIA)	Reactance variations among dengue patients during defervescence of feverintervalis an indicator for classifying risk category in the DHF patients. Clinical Study.	Ibrahim et al., [146]
Other diseases	Critically ill subjects	FM, TBW and ECF (BIS)	Body composition using BIS method show slightly more significant in estimation of FM, TBW and ECF among healthy and diseased subjects. Clinical Study.	Pichler et al., 2013 [91]
	Gastrointestinal disease	R, Xc, Fc, FFM, TBW, ECF and ICF (BIS)	In critically diseased subjects, Fc and ECF increased, Xc decreased, and TBW and ICF remain the same. Clinical Study.	Cox-Reijven et al., 2003 [67]

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6. Conclusions

Increasing demands for accurate, cost effective and non-invasive systems for clinical status monitoring and diagnosis of diseases in healthcare, has accelerated the research endeavors to provide new methods and technologies to eval‎uate the health condition of human body. Body composition assessment tools has been considered a promising approach for the quantitative measurement of tissues characteristic over time, in addition to direct relativity between fluctuations in body composition equivalences and survival rate, clinical condition, illness and quality of life. Bioimpedance analysis is a growing method for body compartments estimation in nutrition studies, sport medicine and eval‎uation of hydration rate, fat mass and fat free mass between healthy and diseased populations. Fat mass, fat free mass including skeletal muscle mass, bone minerals, and total body water, which is composed of intercellular fluid and extracellular fluid, are compartments that can be predicted and analyzed using suitable bioimpedance measurements techniques, procedures and population, age, ethnic groups or disease-dedicated bioimpedance analysis equations. Further studies are needed to eval‎uate the correlations between variations in bioimpedance parameters, especially in ECF and ICF, and the deviation from health to disease.

Acknowledgments

This research is supported by UM High Impact Research Grant UM-MOHE UM.C/625/1/HIR/MOHE/05 from the Ministry of Higher Education Malaysia, Fundamental Research Grant Scheme (FRGS: FP042-2013B) and University of Malaya Research Grant (UMRG: RP009C-13AET).

Author Contributions All authors contributed extensively to the work presented in this paper.

Conflict of Interest

The authors declare no conflict of interest.

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