Classifications of biomedical sensor
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They have been widely used in a lot of fields such as science, medicine, automated manufacturing, environmental monitoring, and so on. Some cheap sensors are finding their ways applying into all sorts of consumer products, from children’s toys, dishwashers to automobiles. To some extent, sensors are multidisciplinary and interdisciplinary field of endeavor. This chapter introduces sensor’s basic definition and features, biomedical sensors, equivalent components in circuit, signal filters and amplifiers, biomeasurement systems and design.
There are a lot of terms which are often used for sensors including transducer, meter, detector, and gage. Defining the term sensor is a very difficult task. At present, there is not a uniform definition which is agreed by all of us. The most widely used definition is that which has been applied to electrical transducer by the Instrument Society of America(ANSI MC 1, 1975):“Transducer —A device which provides a usable output is in response to a specified measurand.” Furthermore, national standard of China points out that sensors consist of sensing component, converting device and electronic circuit. A transducer is more generally defined as a device which converts energy from one form to another. Output of sensor can be an optical, electrical, chemical, or mechanical signal. In the field of electrical engineering, the measurand is physical, chemical, or biological property or condition measured; hence output of biological signal should be an electrical signal, too.
The words sensor and transducer are both commonly used in the context of measurement systems, and often in an interchangeable manner. Transducer is used more in the United States, and sensor has great popularity in Europe and China. The blurring of lines between the exact meaning of sensors and transducers leads to a degree of confusion. Most but not all sensors are transducers, employing one or more transduction mechanisms to produce an electrical output signal. According to the basic sensing principle, sensors are classified into mechanical sensors, electrochemical sensors, biosensors, optical sensors, semiconductor sensors, magnetic sensors, and thermal sensors. From different viewpoints, there are different classifying methods. According to the physical parameters measured by sensors, sensors are classified into resistance displacement sensor, inductive displacement sensor, capacitive displacement sensor, piezoelectric pressure sensor, laser interferometer displacement sensor, bore gagging displacement sensor, ultrasonic displacement sensor, optical encoder displacement sensor, optical fiber displacement sensor, optical beam deformation sensor, flow sensor, imaging sensor, temperature sensor, intelligent sensor and chemical ingredient sensor. Biomedical sensors are used to gain the information on body and pathology, which is a branch of biomedical engineering. Biomedical sensors are classified into physical sensor, chemical sensor and biosensor. Physical sensor could be employed to measure blood pressure, body temperature, blood flux, blood viscosity, biological magnetic field, etc. Chemical sensor is utilized to detect the ingredient and concentration of body liquid such as PH value, Ca+ concentration, glucose concentration, etc. Biosensor is used to sense enzyme, antigen, antibody, hormone, DNA, RNA and microbe. In nature, biosensor is a kind of chemical sensor, which is mainly used to detect biological signals.
Packaging of certain biomedical sensor is an important consideration during the design, fabrication, and use of the device. Obviously, the biomedical sensor has to be safe, soft, and reliable for biomedical sensors often touch the body skin or inner organs of patients. In the development of implantable biosensor, an additional key issue is to consider the biocompatibility of sensor and operational lifetime in body. When a biomedical sensor is implanted into the body, it inevitably contacts with body fluids. Then body will affect the function of biomedical sensor, or sensor will affect the site that it is implanted. For example, protein absorption and cellular deposition can alter the permeability of sensor packaging that is designed to both protect sensor and allow free chemical diffusion of certain analytics between body fluids and the biosensor. Unsuitable packaging of implantable biomedical sensor could lead to drift and a gradual loss of sensor sensitivity and stability overtime. Furthermore, inflammation of tissue, infection, or clotting in a vascular site could produce some harmful or adverse effects on biomedical sensor. Hence, the material used in the construction of sensor’s outer body must be biocompatible because they play a crucial pole in determining an overall performance and longevity of implantable biomedical sensor. One convenient method is to utilize various polymer covering material and barrier layers to prevent the toxic sensor components from coming into body. It’s very important that packaging material of biomedical sensor must prevent the chemical diffusion of harmful ingredient between biomedical sensor and outer body.
Accurate medical diagnostic procedures require the stringent specifications on the design and use of biomedical sensor. Depending on the intended applications, the performance specifications of biomedical sensor may be evaluated to ensure that the measurement meets the design specifications.
In order to understand sensor’s performance characteristics, it is very important to learn some of the common terminology associated with sensor specifications. The following definitions are commonly used to describe sensor characteristics and select sensor for particular applications.
The range of sensor corresponds to the minimum and maximum operation limits that sensor is expected to measure accurately. For example, a pressure sensor may have a nominal performance over the operating range from 0 Pa to 10MPa.
Sensitivity refers to the ratio of output change for a given input change. Another way to define sensitivity is to find the slope of calibration line relating the input to the output, as illustrated in figure 1.A high sensitivity implies that a small change in input causes a large change in output.
For example, a pressure sensor may have a sensitivity of
Input versus output calibration curve of a typical sensor
Accuracy refers to the difference between the true value and the actual value measured by sensor. Classically, accuracy is expressed as a ratio between the preceding difference and the true value; it is specified as a percent of full-scale readings. Here, note that the true value could be traceable to a primary reference standard.
Precision refers to the degree of measurement reproducibility under the same conditions. Very reproducible readings indicate a high precision. Precision should not be confused with accuracy. For an example, measurement may be very precise but not necessary accurate.
When the input is increased from some arbitrary nonzero value, the output of a sensor will not change until a certain input increment is exceeded. Accordingly, resolution is defined as the smallest distinguishable input change that can be detected with certainty.
Reproducibility describes how close measurements are when same input is repeatedly exerted into same sensor under same conditions. When the range of measurement is small, the reproducibility is very high. For example, a temperature sensor may have a reproducibility of±0.1V/℃ for a measurement range from 20℃ to 80℃. Here, what need to be noticed is that reproducibility can vary depending on the measurement range. In other words, readings can be highly reproducible over one range and less reproducible over a different operating range.
Offset refers to the output value when input value is zero, seen in figure 1 (a) and (b).
Linearity of sensor also called nonlinear error of sensor’s characteristic curve; it is a measurement of the maximum deviation between calibration curve and fitting curve. Usually, linearity of sensor is expressed as a percent of full-scale readings or a percent of the actual readings. Linearity could be expressed as the following equation:
Here,
The response time indicates that the time it takes a sensor to reach a percent of its final steady-state value when input of sensor is changed. For example, it takes 10 seconds for pressure sensor to reach 95 percent of its maximum value when a change in pressure of 1Pa is measured. Ideally, a short response time indicates the ability of a sensor to respond quickly to change in input.
Drift refers to the change in sensor reading when the input keeps constant. Drift is divided into temperature drift and zero point drift. Zero point drift refers to the output without any input or with a constant input. Zero point drift could be expressed as the following equation:
Temperature drift refers to the change of output with the change of temperature. It means the deviation of sensor output, which could be expressed as the following equation:
Here,
In some sensors, the input-output characteristic follows a different nonlinear trend, depending on whether input increase or decrease, as in figure 2. For example, a certain pressure sensor could produce a different output voltage when the input pressure varies from zero to full scale and then back to zero. When the measurement is not perfectly reversible, the sensor will show its hysteresis. If a sensor exhibits hysteresis, the input-output relationship is not unique, but depends on the direction change to the input value of sensor.
Input versus output response of a sensor with hysteresis
Biosensor is a kind of device which senses biomaterial and its concentration, and which converts the biosignal into electrical signal. Biosensor has the function of acceptor and converter, which configuration is seen in figure 3. In biosensor, the physicochemical change of the biologically active material resulting from the interaction with the analyte must be converted into an electrical output signal by an appropriate converter. Biosensor’s sensing components mainly have enzymes, cells, antibodies, DNA (Deoxyribonucleic acid), chemical electrode, microbe and other biologically active agents in analytical devices. In the course of detecting the parameters of analytes, biomaterial should be always immobile. In order to develop biosensor, some biotechnology has to be studied and applied, such as DNA biosensor, PH sensor, microelectrode, and so on.
The special features of biosensor are the following:
Biological active material immobilized is used as catalyst, and expensive reagents could be repeatedly used to detect same biological parameters.
Biosensor has intensive specificity. Biomaterial only senses definitive ingredient and it is not affected by color and concentration of measured material.
Biosensor could quickly analyze the result of the measurand.
Biosensor’s accuracy is very high, which relative error could reach one percent.
Biosensor’s analyzing system is very simple.
The cost of biosensor is very low.
According to biological sensing component, biosensor may be divided into five classes: enzyme sensor, microbe sensor, cell sensor, tissue sensor, and immune sensors. According to the signal converter of biosensor, biosensor may be also divided into five classes: bioelectrode sensor, semiconductor biosensor, optical biosensor, piezoelectric biosensor and thermal biosensor. According to the interaction between sensing component and measured material, biosensor can be divided into two classes: affinity biosensor and catalytic biosensor.
Common configure of a biosensor
In biomedical field, main applications of biomedical sensor are as follows:
Detecting the information of clinical chemistry. In the field of medical clinic and basic research, the biology’s information needs to be detected to ensure the present state of given biology. For example, before operating on a patient, a doctor needs to know the body temperature and blood pressure. Under this condition, clinic thermometer and blood sensor has to be employed to help doctor quickly detect body temperature and blood pressure of patient.
Continuously monitoring some parameters of biology outside and inside. In biomedical field, heart frequency has to be monitored continuously by heart sound sensor for a few days after operation. In military, some viruses need to be found by biosensor to hold back the attacking from enemy.
Control. In medicine, people usually utilize some parameter detected by biomedical sensor to control or adjust physiological course of body. In the food industry, biomedical sensor could be utilized to measure some enzyme and its concentration to control the process of fabricating food and to analyze the nutritional ingredient of food. In military, biomedical sensor could be employed to detect the situation of battle field to adjust the strategy of spying or attacking enemy.
Of course, biomedical sensor such as PH sensor could be also employed to detect our atmosphere and condition to improve our living situation.
Many different kinds of sensors can be used in biomedical application. According to the sensing principle in biomedical application, biomedical sensors can be classified into physical sensors and chemical sensors, seen in table 1.
It’s possible to categorize all sensors as being physical or chemical. In the case of physical sensors, quantities such as geometric, mechanical, thermal, and hydraulic variables are measured. In biomedical applications these variables can include things such as muscle displacement, blood pressure, core body temperature, blood flow, cerebrospinal fluid pressure, and bone growth velocity. Two types of physical sensors deserve special mention with regard to their biomedical application: sensors of electrical phenomena in the body, usually known as electrodes, play a special role as a result of their diagnostic therapeutic applications. The most familiar of these are sensors used to pick up the electrocardiogram, an electrical signal produced by the heart. The other type of physical sensor that finds many applications in biology and medicine is optical sensor. These sensors can utilize light to collect information, and, in the case of fiber optic sensors, light is the signal transmission medium as well.
The second major classification of sensing device is chemical sensors. In this case sensors are concerned with the chemical quantities such as identifying the presence of chemical composite, detecting the concentration of various chemical species, and monitoring the chemical activities in the body for diagnostic and therapeutic application. A wide variety of chemical sensors are classified in many ways. Chemical sensors are used to detect chemical components being measured and chemical composition measured in the gas phase. Electrochemical sensors are utilized to measure chemical concentration, or more precisely, activities based on chemical reactions that interact with electrical systems. Photometric chemical sensors are optical devices that detect chemical concentrations based on changes in light transmission, reflection or color. Other types of physical chemical sensors such as the mass spectrometer utilize various physical methods to detect and quantify chemicals associated with biologic systems.
\n\t\t\t\t\t | \n\t\t\t\t\n\t\t\t\t\t | \n\t\t\t
Physical sensors | \n\t\t\t\n\t\t |
\n\t\t\t | Geometric | \n\t\t
\n\t\t\t | Mechanical | \n\t\t
\n\t\t\t | Thermal | \n\t\t
\n\t\t\t | Hydraulic | \n\t\t
\n\t\t\t | Electric | \n\t\t
\n\t\t\t | Optical | \n\t\t
Chemical sensors | \n\t\t\t\n\t\t |
\n\t\t\t | Gas | \n\t\t
\n\t\t\t | Electrochemical | \n\t\t
\n\t\t\t | Photometric | \n\t\t
\n\t\t\t | Other physical chemical methods | \n\t\t
Biopotential electrodes | \n\t\t\t\n\t\t |
\n\t\t\t | Body surface biopotential electrode | \n\t\t
\n\t\t\t | Metal plate | \n\t\t
\n\t\t\t | Intracavitary and intratissue electrode | \n\t\t
\n\t\t\t | Microelectrode | \n\t\t
Bioanalytic (or biosensor) | \n\t\t\t\n\t\t |
\n\t\t\t | Enzyme | \n\t\t
\n\t\t\t | Protein | \n\t\t
\n\t\t\t | Antigen | \n\t\t
\n\t\t\t | Antibody | \n\t\t
\n\t\t\t | Ligand | \n\t\t
\n\t\t\t | Cell | \n\t\t
\n\t\t\t | DNA | \n\t\t
Classifications of biomedical sensor
Although bioanalytic sensors are essentially chemical sensors, they are often classified as a separate major sensor category. These devices incorporate biologic recognition reaction such as enzyme-substrate to identify complex biochemical molecules. The use of biologic reactions gives bioanalytic sensors high sensitivity and specificity in identifying and quantifying biochemical substances.
Measurements of arterial blood gas (pO2 and pCO2) and pH are frequently performed by on critical patients in both the operating rooms and intensive care unit. They are selected and used by the physician to adjust mechanical ventilation or administer pharmacological agents. Such measurement could provide information about the respiratory and metabolic imbalance in the body and reflect the change of blood oxygen increment and carbon dioxide(CO2) elimination.
Noninvasive sensors for measuring O2 and CO2 in arterial blood are based on the discovery that gases such as O2 and CO2 can easily diffuse from body skin. Diffusion occurs due to a partial pressure difference between the blood in the superficial layers of the skin and the outermost surface of the skin. Such idea has been used to develop two types of noninvasive electrochemical sensors pO2 and pCO2. The discovery that blood changes its color depending on the percent of oxygen has led to the development of several optical methods to measure the oxygen saturation in blood.
The method for measuring blood oxygenation is very great important in assessing the circulatory and respiratory condition of a patient. The blood from the lungs to the tissues in two distinct states transports oxygen. Under normal physiological conditions, approximately 2% of the total amount of oxygen carried by the blood is dissolved in the plasma. This amount is proportional to the blood pO2.. The 98% remain is carried inside the erythrocytes in a loose reversible chemical combination with hemoglobin (Hb) as oxyhemoglobin (HbO2). Thus, there are two methods for measuring the blood oxygenation: either using polarographic pO2 sensor or measuring oxygen saturation (the relative amount of hemoglobin dioxide HbO2 in the blood) by means of an optical oximeter.
A pO2 sensor, also widely known as a Clark electrode, is used to measure the partial pressure of O2 gas in a sample of air or blood. This sensor is categorized as an amperometric sensor and requires an external polarization bias source. The measurement is based on the principle of polarography as illustrated in figure 4. The electrode utilizes the ability of oxygen O2 molecules to react chemically with H2O in the presence of electrons to produce hydroxyl (OH-) ions. This electrochemical reaction, called an oxidation/reduction or redox reaction, generates a small current and requires an externally applied constant polarizing voltage source of about 0.6V.
Oxygen is reduced (consumed) at the surface of a noble metal (such as platinum or gold) cathode (this electrode is connected to the negative side of voltage source) according to the following the chemical reaction:
In this reduction reaction, one O2 molecule takes four electrons and reacts with two water molecules, generating four hydroxyl ions. The resulting OH- ions migrate and react with a reference Ag/AgCl anode (this electrode is connected to the positive side of voltage source), causing a two-step oxidation reaction as follows:
Sensing principle of Clark-type pO2 sensor
In this oxidation reaction, silver from the anode electrode is firstly oxidized to silver ions, and electrons are liberated to the anode. These silver ions are immediately combined with chloride ions to form a kind of compound precipitant silver chloride
Electrodes for measuring partial pressure of carbon dioxide CO2 in blood are based on measuring the pH as illustrated in figure 5. The measurement is based on the observation that it forms a weakly dissociated carbonic acid (H2CO3) that subsequently forms free hydrogen and bicarbonate ions when CO2 is dissolved in water according to the following reaction:
As a result of this chemical reaction, the pH of the solution is changed. This change generates a potential between the glass pH and a reference electrode that is proportional to the negative logarithm of the concentration of the carbon dioxide pCO2 in the plasma.
Sensing principle of a pCO2 electrode
The expansion and shrinkage of heart necessarily lead to the vibration of artery that is formed by blood turbulence in vein. When the vibration of artery is transported to the surface of thoracic cavity, heart sound will take place. Heart sound is very valuable for doctor to diagnose many kinds of diseases in our body.
The range of heart sound is from 20Hz to 200Hz. Low limit frequency of heart sound could reach about 4Hz and high frequency limit is greater than 1000Hz. There are many kinds of medical heart sound sensors that are divided into two classifications: air conduction heart sound sensor and direct conduction heart sound sensor. Air conduction heart sound sensor consists of air chamber and common sensor. Such sensor has obvious defects: low sensitivity and easy disturb by surrounding circumstance. Hence, in clinic application, the most sensors applied are direct conduction heart sound sensor.
The sensing structure of piezoelectric acceleration sensor is illustrated in figure 6. Such sensor is used to measure heart sound. Its structure is very simple, which consists of vibration mass block and piezoelectric crystal. A stress spring is utilized to exert a certain stress on vibration mass block between top shell and mass block. Such method could timely adjust the linear characteristic of sensing component. This sensor’s gravity is less than 30g, and is used to detect heart sound and buffeting from body organisms.
Sensing structure of piezoelectric acceleration sensor
Detecting fetus heart sound is very important in clinic application for doctor sometimes needs to grasp the present body status of fetus. PVDF piezoelectric thin film sensor is utilized to be fit for the measurement of fetus’s heart sound as illustrated in figure 7. Its piezoelectric coefficient is the following:
In this structure, silicon rubber converts the vertical motion of itself into the radial motion of PVDF piezoelectric thin film and then corresponding dynamic charge produced by PVDF thin film is proportional to the externally transient force. The voltage along thickness direction is output. Obviously, its work mode is
In the same piezoelectric thin film, one part is used as driving electrode; another is utilized as receiving the sound wave from heart sound.
Dynamic response characteristics on the surface of belly should be considered to well mate belly skin and sensor.
Sensing structure of PVDF piezoelectric acceleration sensor
With the development of sensing technology, more and more heart sound sensors are appearing in our life. Although they have different sensing principle, their functions are alike.
If oxygen and nutrients are to reach tissues, the flow of blood must be maintained in body. Cardiac output flow is often measured as an index of cardiac performance, blood flow through arterial graft is used to ensure that a graft has been successfully inserted during surgery, or the blood flow in peripheral arteries and veins may be measured to assess vascular diseases. There are usually two kinds of measuring methods: one method is direct measurement, sensor is inserted into the blood pipe to sense transient blood flow; another one is indirect measurement, sensor is placed outside vein and senses blood flow by the parameter related to the blood flow. Here, an electromagnetic flow sensor as an example is introduced to demonstrate the measurement of blood flow.
Sensing principle of electromagnetic flow sensor (a) Relation diagram between electrode and magnetic field intensity; (b) Three dimension diagram
Blood flow through an exposed vessel could be measured by means of electromagnetic flow sensor. Electromagnetic flow sensor can be used in biomedicine and science research studies to measure blood flow in major blood vessels near the heart. Such sensor requires that the tested vein must be peeled off and placed into the magnetic gap of sensor. According to the output voltage of sensor, the mean velocity of vein can be calculated and known. And then in terms of the section area tested of vein, the blood flow could be gained finally. According to above idea, the sensing principle of electromagnetic flow sensor is illustrated in figure 7.
Magnetic field intensity
Here,
Electromagnetic blood flow sensor
Practically, this device consists of a clip-on probe that fits snugly around the blood vessel, as illustrated in figure 8. The probe contains electrical coils to produce an electromagnetic field that is transverse to the direction of blood flow. This coil is usually excited by an AC current. A pair of very small biopotential electrodes is attached to the housing and rest against the wall of blood vessel to pick up the induced potential. The flow-induced voltage is an AC voltage at the same frequency as the excitation voltage. Utilizing AC method instead of DC excitation could help to remove any offset potential error due to the contact between the vessel wall and the biopotential electrodes.
Certainly, ultrasonic wave could be also used to detect blood flow of artery. In biomedical application, there are four kinds of ultrasonic wave blood flow sensors according to specific sensing principle and methods: (1) pulse time difference; (2) voice beam deflection; (3) phase shift; (4) Doppler frequency shift. Readers could research biomedical engineering handbook to learn more information.
Respiration measurement often includes two classes: physiological parameter measurement and gas ingredient from respiration system. What sensor the former utilizes is physical sensor, and what sensor the latter employs is chemical sensor and biological sensor. Here, respiration sensor which belongs to the first class is only introduced and explained. The measurement of respiration system is important basis of clinic diagnosis, and it is necessary for patients in the fields of surgery, baby and critically ill patient’s monitoring, sports medicine, and medical research. The measurement of respiration system could be classified into three classes of parameters: respiration frequency, respiration flow and lung respiration volume.
In biomedical research or clinic monitoring, respiration frequency of patient needs to be sometimes detected to record the physiological status. Figure 9 illustrates a kind of sensor for respiration frequency based on thermistor sensing principle. Thermistor is mounted to the front-end of binder. When binder clamps the nares, airstreams from body flows through the surface of thermistor. According to the change of thermistor value, the respiration frequency would be measured.
Thermistor sensor for respiration frequency (a)structure diagram, (b)measurement diagram
Of course, elastic strain instrument could be also utilized to detect the respiration frequency. Its sensing principle is such: resistance wire is fixed to the surface of elastic plastic pipe. And then mercury or other electrolyte is sealed into the elastic plastic pipe. After elastic plastic pipe is adhered to the front of breast, respiration would lead to the length change of elastic plastic pipe. Such length change causes the change of resistance wire which could show the change of respiration frequency. When resistance wire is introduced into a detecting circuit, the respiration frequency will be sensed and measured.
If blood circulation is to be maintained in the body, tissues are to be perfused with oxygen. Then correct pressure measurement has to be applied in the vascular system. The usual blood pressure methods have: liquid coupling direct measurement, pipe-end sensing measurement, indirect blood pressure sensing measurement. Liquid coupling direct measurement means that the pipe filled with liquid is inserted into the measured part and that the pressure is measured by liquid coupling of pipe end position in the body, which is the simplest method. Pipe-end sensing measurement employs pipe-end sensor to measure blood pressure. Pipe-end sensor which can convert the pressure signal into electronic signal is placed on the measured part. And then the electronic signal measured is transmitted to the external wire. Such method could avoid the distortion of signal of blood pressure. Pipe-end sensing measurement has a lot of advantages, but such method needs to activate the skin and relative sensors have to been placed into the body. Hence indirect blood pressure measurement is noted by people and continuously explored. Blood-pressure meter is a classic example of indirect blood pressure measurement, which is shown in figure 10.
Sensing principle of indirect blood pressure measurement
In figure 10, the sensing principle is based on Coriolis sound. Gas is filled into cuff to hold back the arterial blood flow. And then gas in cuff is sent out slowly to monitor whether there appears arterial blood flow at the downstream of arterial blocking point. Here, the employed sensor is common mercury pressure meter. And such method is up to the actual experience of staff. When coriolis sound is heard, namely when blood flows through artery blood pipe, blood pressure in cuff is shrinking pressure in artery pipe. When blood flows recover normal level, blood pressure in cuff is diastolic pressure of artery. Systole pressure and diastolic pressure are recorded as blood pressure. Such method is not harmful to the skin or organ in the body.
Biopotential measurements are made using different kinds of specialized electrochemical electrodes. The function of electrodes is to couple the ionic potentials generated inside the body to an electronic instrument. Biopotential electrochemical electrode is classified either as noninvasive (e.g. skin surface) or invasive (e.g. microelectrode, wire electrode) electrodes. When a metal is placed in an electrolyte solution, a charge distribution is created next to the metal/electrolyte solution interface as illustrated in figure 11. The localized charge distribution causes an electronic potential by electrochemical electrode, called half-cell potential, to be developed across the interface between metal electrode and electrolyte solution.
The charge distribution at a electrolyte/metal interface
The half-cell potentials of several important metals are listed in table 2. Here, a point needs to be pointed out that hydrogen electrode is considered to be a standard electrode against which the half-cell potentials of other metal electrodes are measured.
Silver and zinc electrodes are immersed in an electrolyte solution. And then we may calculate the potential drop between two electrodes. From table 2, the half-cell potentials for silver and zinc electrodes are 0.799V and -0.763V respectively. Hence, the half-cell potentials between two electrodes are equal to the following value:
Typically, utilizing the electrochemical electrodes composed of the same metals could measure the half-cell potentials. Hence, the two half-cell potentials for these electrodes would be equal in magnitude. Some common electrodes are introduced here, which is utilized as a sensor.
A typical flexible biopotential electrode for ECG (electrocardiogram, ECG) recording is composed of certain polymers or elastomers which are made electrically conductive by the addition of a fine carbon or metal powder. These electrodes as illustrated in figure 13a are available with prepasted AgCl gel for quick easy application to the skin using a double-sided peel-off adhesive tape. The most common type of biopotential electrode is the silver/silver chloride electrode (Ag/AgCl), which is formed by electrochemically depositing a very thin layer silver chloride onto the surface of silver electrode as illustrated in figure 13b. These electrodes are recessed and imbedded in foam that has been soaked with an electrolyte paste to provide good electrical contact with the skin. The electrolyte saturated foam is also known to reduce motion artifacts which are produced during stress testing when the layer of the skin moves relative to the surface of the Ag/AgCl electrode. This motion leads to the large interference in the recorded biopotential and, in the extreme cases, could severely degrade the measurement.
\n\t\t\t\t\t | \n\t\t\t\t\n\t\t\t\t\t | \n\t\t\t
Al → Al3++3e-\n\t\t\t | \n\t\t\t-1.706 | \n\t\t
Cr → Cr3++3e-\n\t\t\t | \n\t\t\t-0.744 | \n\t\t
Cd → Cd2++2e-\n\t\t\t | \n\t\t\t-0.401 | \n\t\t
Zn → Zn2++2e-\n\t\t\t | \n\t\t\t-0.763 | \n\t\t
Fe → Fe2++2e-\n\t\t\t | \n\t\t\t-0.409 | \n\t\t
Ni → Ni2++2e-\n\t\t\t | \n\t\t\t-0.230 | \n\t\t
Pb → Pb2++2e-\n\t\t\t | \n\t\t\t-0.126 | \n\t\t
H2 → 2H++2e-\n\t\t\t | \n\t\t\t0.000(stand by definition) | \n\t\t
Ag → Ag++e-\n\t\t\t | \n\t\t\t+0.799 | \n\t\t
Au → Au3++3e-\n\t\t\t | \n\t\t\t+1.420 | \n\t\t
Cu → Cu2++2e-\n\t\t\t | \n\t\t\t+0.340 | \n\t\t
Ag+Cl → AgCl+2e-\n\t\t\t | \n\t\t\t+0.223 | \n\t\t
Half-cell Potentials of Important Metals
Biopotential skin surface ECG electrode
Electrochemical electrodes are also used to record electromyography (EMG) signals from different muscles in the body. The body and size of the recorded EMG signals depends on the electrical property of these electrodes and the recording location. For invasive recordings, proper skin preparation, which normally involves cleaning the skin with alcohol or the application of a small amount of an electrolyte paste, helps to minimize the impedance of the skin-electrode interface and to improve the quality of recording signal considerably. The most common electrodes used for the surface EMG recording and nerve conduction studies are circular discs, about 1 cm in diameter, that are made of silver or platinum. For direct recording of electrical signals from nerves and muscle fibers, a variety of percutaneous needle electrodes are available as illustrated in figure 14. The most common type of needle electrode is the concentric bipolar electrode as illustrated in figure 14a. This electrode is made from the thin metallic wires encased inside a larger canola or hypodermic needle. The two wires serve as the recording and reference electrodes.
Intramuscular biopotential electrode:(a)bipolar electrode, (b)unipolar configuration
Another type of percutaneous EMG electrode is the unipolar needle electrode as illustrated in figure 14b. This electrode is made of a thin wire that is most insulated by a thin layer near the distal tip. Unlike bipolar electrode, this type of electrode requires a second unipolar reference electrode to form a closed electrical circuit. The second recording electrode is normally placed either adjacent to the recording electrode or attached to the surface of our skin.
The most commonly used electrode for recording electroencephalographic (EEG) signals from the brain are cup electrodes and subdermal needle electrodes. Cup electrodes are made of platinum or tin and are approximately 5-10mm in diameter. The cup electrodes are filled with an electrolyte gel and can be attached to the scalp with an adhesive tape.
Recording the biopotentials from the scalp is very difficult because hair and oily skin hold back the good electrical contact. Hence, clinicians sometimes prefer to use subdermal needle electrodes (EEG electrodes) instead of the metal surface electrodes for EEG recording. These electrodes are both fine platinum or stainless-steel needle electrodes about 10mm long by 0.5mm wide, which are inserted under the skin to provide a better electrical contact.
Microelectrodes are biopotential electrodes with ultra-fine tapered tip that can be inserted into biological cells. These electrodes play a very important role in recording action potentials from single cells and are used in neurophysiologic studies to comprehend the course of biological information conversion and transmission in our body. The tip of these electrodes must be very small with respect to the dimensions of the biological cell to avoid cell damage and at the same time sufficiently strong to penetrate the cell wall. The electrode which is applied to microbe studies is called microelectrodes. Generally, there are three types of microelectrodes: (1) glass microelectrodes, (2) metal electrodes, and (3) solid-state microprobes.
For glass microelectrodes, when the tip of such electrodes is inserted into an electrolyte solution, such as the intracellular cytoplasm of a biological cell, ionic current can flow through the fluid junction at the tip of the microelectrode. Such mode could establish a closed electrical circuit between two Ag/AgCl wire electrodes inside the microelectrode and biological cell. For metal electrode, when the tip of such microelectrodes is usually sharpened down to a diameter of a few micrometers by an electrochemical etching process. The wires are then insulated up to its tip.
Solid-state microfabrication techniques commonly used in the production of the integrated circuits can be used to produce microprobes for multichannel recordings of biopotentials or for electrical stimulation of neurons in our brain or spinal cord. Most of solid-state microelectrodes are microsensor actually. Such probe consists of a precisely micromachined silicon substrate with four exposed recording sites. One of main advantages of microfabrication techniques is the ability to mass produce very small and highly sophisticated microsensors with highly reproducible electrical and physical properties.
Enzyme constitutes a group of more than 2000 proteins having so-called biocatalytic properties. These properties give the enzymes the unique and powerful ability to accelerate chemical reactions inside biological cells. Most enzymes react only with specific substrates even though they can be contained in a complicated mixture with other substances. It is important that soluble enzymes are very sensitive both to temperature and pH variations, and they can be inactivated by many chemical inhibitors. For practical biosensor applications, these enzymes are normally immobilized by insolubilizing the free enzymes via entrapment into an inert and stable matrix such as starch gel, silicon rubber, or polyacrylamide. This process is very important to ensure that the enzymes retains its catalytic properties and can be reusable.
The action of specific enzymes may be utilized to form a range of different biosensors. A typical example of enzyme-based sensor is a glucose sensor that uses the enzyme glucose oxidase. Glucose plays an important role in metabolic process. Currently, available glucose sensors are based on an immobilized enzyme, such as glucose oxidase, which acts as a catalyst. Glucose is detected by electromechanically measuring either the amount of gluconic acid or hydrogen peroxide (H2O2) produced or by measuring the percent of oxygen consumed according to the following chemical reaction:
A glucose sensor is similar to a
Sensing principle of glucose sensor
Biocatalytic enzyme-based sensors generally consist of an electrochemical gas-sensitive converter or an ion-selective electrode with an enzyme immobilized in or on a membrane that serve as the biological mediator. The analyte diffuses from the bulk sample solution into the biocatalytic layer where an enzymatic reaction takes place. The electroactive product that is formed (or consumed) is usually detected by an ion-selective electrode. A membrane separates the basic sensor from the enzyme if a new gas is produced (such as CO2 or NH3) or consumed (such as O2). Although the concentration of the bulk substrate drops continuously, the rate of consumption is usually negligible. The decrease is detected only when the test volume is very small or when the area of enzyme membrane is large enough. Thus this electrochemical analysis is nondestructive, and the sample is reused. Measurements are usually performed at a constant pH and temperature either in a stirred medium solution or in a flow through solution. In order to control biochemical process including some enzyme sensors, a number of microbial sensors have been continuously developed and applied to various environment, agriculture, food and pharmaceutical.
Microbial sensors typically involve the assimilation of organic compounds by microorganisms, followed by a change in respiration activity(metabolism) or the production of specific electrochemically active metabolites, such as CO2, H2, or NH3, that are secreted by the microorganism.
A microbial sensor is composed of immobilized microorganisms that serve as specific recognition elements and an electrochemical or optical sensing device that is used to convert the biochemical signal into electronic signal that can be processed. The operation of a microbial sensor can be described by the following five-step process:
The substrate is transported to the surface of the sensor;
The substrate diffuses the membrane to the immobilized microorganisms;
A reaction occurs at the organism;
The products formed in the reaction are transported through the membrane into the surface of detector;
The product is measured by the detector.
Here, an example of a microbial sensor is given to demonstrate the detecting course of microbial sensor including ammonia (NH3) and nitrogen dioxide (NO2) sensors that utilize the nitrifying bacteria as the biological sensing component. A NH3 biosensor can be constructed on the base of nitrifying bacteria that uses ammonia (NH3) as a source of energy and oxidizes ammonia as follows:
Sensing principle of a NO2 microbial biosensor
This oxidation process proceeds at high rate, and the amount of oxygen consumed by the immobilized bacteria can be measured directly by a polarographic oxygen electrode placed behind the bacteria.
Nitric oxide (NO) and NO2 are two principal pollution gases of nitrogen in the atmosphere. The principle of a NO2 biosensor is shown in figure 16. When a sample of NO2 gas diffuses through the gas-permeable membrane, it is oxidized by the nitrosomonas bacteria as follows:
Similar to an ammonia biosensor, the consumption of oxygen O2 around the membrane is determined by an electrochemical oxygen electrode.
Many biomedical instruments utilize a sensor to convert a signal created by the body into an electrical signal. In medicine, the electrical circuits and electrical components are often utilized to detect the biomedical signal by sensor. After basic electrical components and biomedical sensors are connected together, a bioinstrumentation is then formed. Hence, describing a bioinstrumentation could begin with charge, current, voltage, power and energy. In this section, these basic variables will be introduced and explained.
In our life, there are two kinds of charge, negative and positive, and they are carried by the protons and electrons, respectively. The negative charge,
The symbol,
Electrical current,
and
A simple circuit illustrating current flowing around a closed loop
In addition to the above definition, current also depends on the direction of flow, as illustrated in figure 17 Current is defined as positive if
A positive charge is moving in the direction of arrow;
A negative charge is moving in the opposite direction of arrow.
A sample current waveform and its electrical circuit
Since these two cases cause the same outcome, there is no need to be concerned as to which is responsible for the current. In electrical circuits, current is carried by electrons in metallic inductors.
Consider the waveform in figure 18, with the current entering into terminal1 in the circuit on the right, the current in the time interval 0 to 1.5 second, is positive and enters terminal1. The current in the time interval 1.5 to 3 second, is negative and enters terminal2 with positive value. If there are no current changes in the time interval 0 to 3s, the curve of current will be a line. Then the electrical circuit in figure 18 is constant which is called direct current (DC) indicating that it does not change with time. We denote a time-varying current with lowercase letter, such as
Current can only flow in a closed circuit. Kirchhoff’s current law is used to ensure the relationship among every branch of circuit at same point. For current is continuous, any a point in circuit can not accumulate charge. Hence, at any time and any node, the sum of the currents which flow same node is equal to the sum of the currents which outflow from same node. This principle is known as Kirchhoff’s current law (KCL).
In circuit as illustrated in figure 19, the current at the node,
or, above formula is adjusted into the following equation:
Namely,
At any time, the algebraic sum of the currents at a node is equal to zero. It should be clear for all currents whether they are all leaving or entering the node.
Node of circuit
Voltage and current convention
In describing a circuit, we define its characteristics with terms node, branch, path, closed path, and mesh as follows:
Node: A point at which two or more circuit elements have a common connection.
Branch: A circuit element or connected group of circuit elements. A connected group of circuit elements usually connect nodes together.
Path: A connected group of circuit elements in which none is repeated.
Closed Path: A path that starts and ends at the sam node.
Mesh: A closed path that does not contain any other closed paths within it.
Essential Node: A point at which three or more circuit elements have a common connection.
Essential Branch: A branch that connects two essential nodes.
Kirchhoff’s current law could be also applied to any closed surface surrounding a part of the circuit. It’s understood that the closed surface does not intersect any of the circuit elements.
Voltage represents the work per unit charge associated with moving a charge between two points (A and B in figure 20) and that is given as the following formula:
The unit of measurement for voltage is the volt (V). A constant voltage source is denoted by the letter V, while a time-varying voltage is denoted by the lowercase letter
Kirchhoff’s voltage law is utilized to ensure the voltage relationship at any branch of circuit. Starting from any point of circuit, the sum of potential drop at the closed branch along the clockwise or counterclockwise direction is equal to the sum of potential rise.
Circuit loop
In figure 21, the reference direction of electromotive force, current and branch voltage is marked. Cycling one circle along virtual line given in circuit, the following equation could be listed out:
Above equation could be also written into the following equation:
Namely,
According to above voltage equation, the algebraic sum of branch voltage is equal to zero along any a closed branch circuit. If it is stipulated that potential drop is negative, potential rise is positive.
Kirchhoff’s laws are applied in electrical circuit analysis to determine unknown voltages and currents. Each unknown variable has its distinct equation. To solve for the unknowns using MATLAB, we create a matrix representation of the set of equations and solve them using the matrix calculation techniques.
Power is the rate of energy expenditure given as:
Where, the letter,
Polarity references for four cases of current and voltage. Cases (a) and (d) result in positive power being consumed by the circuit element. Cases (b) and(c) result in negative power being extracted from the circuit element.
Figure 22 illustrates the four possible cases for a circuit element’s voltage and current configuration. According to the convention, if current and voltage are positive, with the arrow and polarity shown in figure 22, energy is absorbed. If either the current arrow or the voltage polarity is reserved, as in (b) and (c), energy is supplied to the circuit. If both the current direction and voltage polarity are reserved together as in figure 22(d), energy is absorbed.
Basic symbol for independent source
A passive circuit element is defined as an element whose power is always positive or zero, which is dissipated as heat (resistance), stored in an electric field (capacitor), or stored in magnetic field (inductor). We define an active circuit element as one whose power is negative and capable of generating energy. Energy is given by the following equation:
In circuit, the basic source symbol is listed in figure 23.
In figure 24, the direction of current and voltage is the same. According to Ohm’s law, the following formula could be given:
Resistance and its symbol
The parameter of resistance is gained:
This parameter is called resistance which has the property of holding back the current in circuit. And it is denoted with the symbol in figure 24b. Here, this relationship could be applied at very high voltage and current. Some electrictronic materials have a very small range of currents and voltages where they exhibit linear behavior. In reality, some material is linear only within a range of values. Outside this range, resistance is not linear. In circuit, we define:(1) having a 0V voltage drop when R=0;(2)having a 0current through resister when R=∞.
Each material has a property called resistivity(ρ) that indicates the resistance of the material. Conductivity is the inverse of resistivity, and conductance (G) is the inverse of resistance. Conductance is measured in unit called siemens(S) and has the unit of A/V. In terms of conductance, ohm’s law could be written as:
For formula
This formula demonstrates that electrical energy is all consumed by resister component. And the energy is converted into thermal energy, that’s to say, resister is a consuming-energy component.
If the same current flows from one resister to another, the two are said to be in series. If these two resisters are connected to the third and the same current flows through all of them, then the three resistors are in series. Consider figure 25 with three resisters in series, an equivalent circuit can be derived through Kirchhoff’s Voltage Law as follows:
A series circuit
Above equation can be also rewritten as:
Where, the equivalent resistance,
A parallel circuit
Two or more resisters are said to be parallel if the same voltage is across each of resisters. Consider the three parallel resisters as illustrated in figure 26, a equivalent circuit for figure 26 is derived through Kirchoff’s Current Law as
Above equivalent resistance can be also rewritten as:
In general, if there are
A capacitor in figure 27 is a device that stores energy in the electrical field by charge separation when appropriately polarized by the voltage. Simple capacitors consist of parallel plates of conducting material that are separated by a gap filled with a dielectric material. Dielectric materials that are air or mica contain a large number of electric dipoles that become polarized in the presence of electric field. The charge separation caused by the polarization of the dielectric is proportional to the external voltage and given by the following equation:
Where the symbol,
When the charge or voltage of capacitor changes, the produced current in circuit is given as:
This equation is given on the base of the same direction of current and voltage; otherwise there should be a negative symbol in this equation.
The capacitance of capacitor is determined by the permittivity of the dielectric,
When a constant voltage is exerted on the both sides of capacitor and its current is zero, this capacitor is considered as an open circuit or DC circuit. In physical structure, capacitor consists of two conducting surfaces that store charge, separated by a thin insulating material that has a very large resistance.
For the equation
Above equation demonstrates that the electric energy increases with the increase of voltage on the capacitor, and in the course, the capacitor component acquires electric energy from electric source. Formula
Circuit with a capacitor
Circuit with inductor
For the equation
If
and for
The initial voltage in above equation,
An inductor in figure 28 is a passive element that is to store energy in magnetic field and is made by winding a coil of wire around a core that is a insulator or a ferromagnetic material. A magnetic field is established when current flows through the coil. The symbol is utilized to represent the inductor in a circuit. The unit of measurement for inductance is the Henry or Henries (H). The relationship between voltage and current for inductor is given by
The convention for writing the voltage drop across an inductor is similar to that of a resistor.
Physically, current cannot change instantaneously through a inductor since an infinite voltage required. Mathematically, a step change in current through an inductor is possible by applying a voltage. For convenience, when a circuit has just DC currents (or voltages), the inductors can be replaced by short circuits, since voltage drops across the inductors are zero.
After producing current on the both sides of equation, the following expression can be acquired after integration:
Above expression demonstrates that magnetic energy increases with the increase of current through inductor component. In this course, electrical energy could be converted into magnetic energy, namely inductor acquires energy from the source. Formula
For the equation
If
and for
The initial current in above equation,
Biosignals are recorded as potentials, voltages, and electrical field strengths generated by nerves and muscles. The measurements involve voltages at very low levels, typically ranging from 1μV to 100mV, with high source impedances and superimposed high level interference signals and noise. The signals need to be amplified to make them compatible with devices such displays, recorders, or A/D converters for computerized equipment. Amplifiers adequately to measure these signals have to satisfy very specific requirements. They have to provide amplification selective to the physiological signal, reject superimposed noise and interference signals, and guarantee protection from damages through voltage and current surges for both patient and electronic equipment. Amplifiers featuring these specifications are known as biopotential amplifiers.
The basic requirements that a biopotential amplifier has to satisfy are:
The physiological process to be monitored should not be influenced in any way by the amplifier.
The measurement signals should not be distorted.
The amplifier has to provide protection of patient from any hazard of electrical shock.
The amplifier itself has to be protected against damages that might result from high input voltages as they occur during the application of defibrillators or electrosurgical instrumentation.
Typical configuration for the measurement of biopotentials
A typical configuration for the measurement of biopotentials as illustrated in figure 29. Three electrodes, two of them are used to pick up the biological signal and the third providing the reference potential, connect the subject to amplifier. The input signal to the amplifier consists of five components:(1) the desired biopotential, (2)undesired biopotential, (3) a power line interference signal of 60Hz (50Hz in some countries) and its harmonics, (4)interference signal generated by the tissue/electrode interface, and (5) noise. Proper design of the amplifier provides rejection of a large portion of the signal interferences. The main task of designing deferential amplifier is to reject the line frequency interference that is electrostatically or magnetically coupled into subject. The desired biopotential appears as a voltage between two input terminals of differential amplifier and is referred to as the differential signal. The line frequency reference signal shows only small differences in amplitude and phase between the two measuring electrodes, causing approximately the same potential at both inputs, and thus appears only between the inputs and ground and is called common mode signal. Strong rejection of the common mode signal is one of the most important characteristics of a good biopotential amplifier.
In order to provide optimum signal quality and adequate voltage level for further signal processing, amplifier has to provide a suitable gain range and needs to maintain a possible signal-to-noise ratio. The presence of the high level interference signals not only deteriorates the quality of the physiological signals, but also restricts the design of the biopotential amplifier. For example, electrode half-cell biopotentials limit the gain factor of the first amplifier stage since their amplitude can be several orders of magnitude larger than the amplitude of physiological signal. To prevent the amplifier from going to saturation, this component has to be eliminated before the required gain be provided for physiological signal.
Schematic design of the main stages of a biopotential amplifier. Three electrodes connect the patient to a preamplifier stage. After removing DC and low frequency interference, biological signal is connected to an output low-pass filter through an isolation stage which provides electrical safety to the patient, prevents patient loops, and reduces the influence of interference signals.
A typical design of the various stage of a biopotential amplifier is shown in figure 30. The three electrodes which provide the transition between the ionic flow of currents in biological tissue and electronic flow of currents in amplifier represent a complex electrochemical system. To a large extent, these electrodes determine the composition of the measured signal. The preamplifier represents the most critical part of a amplifier since it sets the stage for the quality of the biosignal. With proper design, the preamplifier can eliminate, or at least minimize, the most signal interfering with the measurement of biopotentials. In addition to electrode biopotentials and electromagnetic interference, noise which is generated by the amplifier and the connection between biological source and amplifier has to be taken into account when designing a preamplifier.
Four types of filters and its amplitude-frequency characteristics
After biosignals are preamplified, some unuseful signal have to be eliminated or filtered to highlight the useful biosignal. Such function can be realized by all kinds of filters. In circuit, according to the frequency range of signals there are four classes of filters: low-pass filter (LPF), high-pass filter (HPF), band-pass filter (BPF) and band elimination filter (BEF). These four types of filters are shown in figure 31.
Operational amplifiers play an important role that they amplify a weak signal and adjust voltage or current in detecting circuit. An operation amplifier is an electronic device that consists of plenty of transistors, resistors, and capacitors. Fully understanding its operation requires that people have the knowledge of diodes and transistors. Circuit involving operational amplifier forms the cornerstone of any bioinstrumentation, from amplifiers to filters. Amplifiers used in biomedical applications have very high-input impedance to keep the current down from the system being measured. Most body signals have small magnitudes. For example, ECG has a magnitude in millivolts and the EEG has a magnitude in microvolt. Analog filters are often used to remove noise from a signal, typically through frequency domain analysis to design the filter.
\n\t\t\t\t | \n\t\t\t\t\t | \n\t\t\t\t\n\t\t\t\t\t | \n\t\t\t\t\n\t\t\t\t\t | \n\t\t\t
Circuit Constitution | \n\t\t\t\n\t\t\t\t Requi rement: R2=R1//RF\n\t\t\t | \n\t\t\t\n\t\t\t\t Requirement: R2=R1//RF\n\t\t\t | \n\t\t\t\n\t\t\t\t Requirement: R1=R’\n\t\t\t\t1, RF=R’\n\t\t\t\tF\n\t\t\t | \n\t\t
Voltage amplification factor | \n\t\t\tOutput and input voltages are inverse | \n\tOutput and input voltages are noninverse | \nWhen R1=R’\n1, RF=R’\nF\n | \n
| \n | \n | \n | \n
| \nLow | \nLow | \nLow | \n
Performance characteristics | \n\t∎ Realize inverse proportional operation. ∎ Cite parallel voltage negative feedback. ∎ Virtual ground, low common-mode input voltage. ∎ Low input and output resistance. | \n\t∎ Realize noninverse proportional operation. ∎ Cite series voltage negative feedback. ∎ Virtual short, but not virtual ground, high common-mode input voltage. ∎ High input resistance and low output resistance. | \n\t∎ Realize subtract operation. ∎ Virtual short, but not virtual ground, high common-mode input voltage. ∎ Low input and output resistance. ∎ High requirement of component symmetry. | \n
Comparison of three types of scaling operation circuits
The operational amplifier is an amplifier, but when it is combined with other circuit elements, it may integrate, differentiate, product, divide, sum, and subtract. In circuit, there are three basic types of proportional operation amplifiers: inverse scaling operation circuit, noninverse scaling operation circuit, and differential scaling operation circuit. These three types of operation circuit are compared as illustrated in table 3.
According to the information listed in table 3, we could know that operational amplifier is drawn with the symbol in figure 32. The input terminals are labeled the no inverting input (+) and inverting input (-). The power supply terminals are labeled
Circuit element symbol for the operational amplifier
Figure 33 shows an ideal mode of op amp, focusing on the internal behavior of input and output terminals. The input-output relationship is the following:
An internal mode of the op amp
Idealized mode of the op amp
Since the terminal resistance is very large, we may replace it with an open circuit to simplify analysis, leaving us with the op amp model shown in figure 34.
With the replacement of the internal resistance in an open circuit, the input current is zero (
Find the output voltage
Using the op amp model shown in figure 33, we may apply KCL at the inverting terminal and gain the following:
since currents do not flow into the op amp’s input terminals. Replacing the current using ohm’s law gives:
Multiplying by R1R2 and collecting like terms, we could gain:
Now
Substituting
Namely,
When a goes to infinity, the above equations could be simplified into:
Interestingly, with A going to infinity, output voltage
Biological signals are often very small and typically contain some unwanted noise or interference. Such interference could determine the effect of obscuring relevant information that may be available in the measured signal. Noise can be extraneous in nature, arising from sources outside the body, such as thermal noise in sensors or noise in the electronic components of the acquisition system. Noise can be intrinsic to the biological media, meaning that it can arise from adjacent tissues or organs. ECG measurement from the heart can be affected by bioelectric activity from the adjacent muscles.
In order to extract the meaningful information from biological signals, sophisticated bioinformation acquisition techniques and equipment are commonly utilized and explored. Equipments with high-precision low-noise are very necessary to minimize the effect of unwanted noise. Basic components include sensors, amplifiers, analog signal conditioner, data acquisition, data storage and display, digital signal processing circuit. The bioinformation acquisition procedure is shown in figure 35.
Procedure of obtaining biological information
In figure 35, sensors feel the biological signal that is being observed into an analog signal conditioner to adapt the requirement of data acquisition system. Here data acquisition system converts the analog signals into a calibrated digital signal that can be stored. Digital signal processing techniques are employed here to reduce the noise and extract additional information that can improve understanding of physiological meaning of original parameter. Throughout the data acquisition shown in figure 35, it’s very critical that the information and structure of original biological signal of interests be faithfully preserved. Because these signals are often used to help people diagnose the pathological disorder. The procedure of analog signal conditioner, data acquisition system, analog amplifying and signal filtering, and A/D conversion should not generate misleading or untraceable distortion. Signal distortion would lead to an improper diagnosis on biological body.
In bioinstrumentation, after biological signal has been detected with an appropriate sensor, it is amplified and filtered. Operational amplifiers are electronic circuits that are used to adjust the amplitude or size of biological signal. Analog filter may be used to remove the noise hiding in biological signal or compensate for distortions caused by sensors. Amplification and filtering of biological signal may be necessary to meet the requirement of hardware specifications of signal conversion procedure. Continuous signal needs to be limited to a certain band of frequencies before signal can be digitized with an analog-to-digital converter, prior to storing in a digital computer.
The biomeasurement system is shown in figure 36 to measure some biological signals such as quantity, property, or condition which are bioelectrical signal generated by muscles or the brain, or a chemical or mechanical signal that is converted into an electrical signal. Biomeasurement system is composed of sensor, analog processing circuit, A/D conversion, digital signal processing, output display, and data storage. A/D conversion is used in bioinstrumentation to acquire the enough system gain.
Basic biomeasurement system using sensors to measure a biological signal with data acquisition, storage and display capabilities, data transmission, along with control and feedback
With the invention of telephone and with appearance of internet, signal can be required with a device in one location, perhaps in patient’s home, and transmitted into another device for transmission or storage. For example, if a biological signal from bioinstrumentation system in rural area could be transmitted into a diagnosis center in hospital, doctor would quickly judge some diseases to make patients gain an accurate treatment or diagnosis in time.
Two other components play important roles in bioinstrumentation system. The first is the calibration signal. A signal with known frequency and amplitude is applied to the bioinstrumentation system at sensor’s input. The calibration device permits the system components to be adjusted so that it’s known that the output and input have a certain linear relationship. Without such information, it’s impossible to convert the output of an instrument system into a meaningful representation of the measurand.
Another important component, a control or feedback element, is not a part of all instrument systems. These parts include pacemakers and ventilators that could stimulate the heart and lungs. Some feedback devices collect physiological data and stimulate a response— a beat or breath—when needed or are part of biofeedback systems in which patients are made aware of a physiological instrument, such as blood pressure, and uses conscious control to change the physiological response.
Figure 36 shows the basic elements which constitute basic bioinstrumentation system. Circuits play a very important role in bioinstrumentation system. If a bioinstrumentation needs to be developed or improved to be fit for new condition, function circuits in different blocks from figure 36 have to be respectively designed to form bioinstrumentation system with relative indexes. Among all kinds of circuits, amplifiers and A/D converters are very important component for detecting the biological signal. Hence, amplifying circuits will be only introduced here in detail, and other function circuits could be read or utilized in relative books.
Bioelectric amplifier
In order to record the bioelectric potential from the body, biological amplification is always required. The simplest form is shown in figure 37 which uses a single-input amplifier. Here amplifier only amplifies one input signal which is applied in the input and the reference “earth” or “ground”.
In this amplifier, the resistor
Unfortunately, in circuit shown in figure 37, the resistor
A simplest single-input amplifier
A differential amplifier
There is also capacitor introduced in figure 37 in series with the input signal. Capacitor
If capacitor C is 1μF and resistor
Unfortunately, even with capacitor C added, this type of amplifier is not suitable for recording small bioelectric signal because of interference from external electric fields. An electric electrode has to be connected to the amplifier via a wire and this wire is exposed to interfering signals. However, the interference will only appear on the input wire to the amplifier and not on the “ground” wire which is held at zero potential. An elegant solution to this problem is to utilize differential amplifier as shown in figure 38. The input of the type of amplifier has three connections marked ‘+’, ‘-’ and ‘ground’.
Differential amplifier
In figure 38, the signal which we wish to record is connected between the ‘+’ and ‘-’ points. Now both inputs are exposed to any external interfering electric fields so that the difference between the ‘+’ and ‘-’ input will be zero. This will not be quite true because the electric fields experienced by the two input wires may not be exactly the same, but if the wires are run close together then the difference will be small. Differential amplifier is not perfect in that even with the same signal applied to both inputs, with respect to ground; a small output signal can appear. This imperfection is specified by the common mode rejection ratio or CMMR. An ideal differential amplifier has zero output when identical signals are applied to the two ‘+’ and ‘-’ inputs. CMMR could be defined as the following equation:
Where, signal and common-mode gains are given by
In practice, common-mode voltage
Hence, the required CMMR could be given as:
In fact, it’s not always easy to achieve a CMMR of 100dB. As we have known, electrode source impedances have a very significant effect on CMMR and hence electrode impedance affects noise rejection.
Of course, in detecting biosignals, the AC coupling shown in figure 37 and figure 38 degrades the performance of the amplifiers. If the input impedance and bias current of amplifiers is sufficiently high, then they can be connected directly to the input electrodes, without producing electrode polarization. Furthermore, DC offset will occur from the electrode contact potentials, but if the amplifier gain is low (<10) DC offset will be not a significant problem. The offset can be removed by AC coupling at later stage.
However, there are some safety arguments against the use of DC coupling. If a fault arises in the operational amplifier, then it’s possible for the power supply to be directly connected to the patient and so give rise to a hazard. DC currents will cause electrolysis and result in tissue necrosis. AC coupling could avoid this problem and is often used. Nonetheless DC coupling is also often used in biomedical field.
The purpose of using bioinstrumentation is to monitor the output of a sensor or sensors and to extract some useful information from signals that are produced by sensors.
Acquiring discrete-time signal and storing this signal in computer memory from a continuous-time signal is accomplished with analog-to-digital (A/D) converter. After analog signals have been processed which are based on analog filters such as low-pass or high-pass filters, A/D converter uniformly samples the continuous-time waveform and transforms it into a sequence of numbers, one every
Biological signal categories in human body
The electrical, chemical and mechanical activity that occurs during this biological event often produces signals that could be detected and analyzed. Biological signals are the record of a biological event such as a beating heart or a contracting muscle. Hence, biological signals contain useful information which could reflect human’s activities and physiology, that’s to say, biological signal could be used for biomedical diagnosis. Biological signals are classified into bioelectric signals, biomagnetic signals, biochemical signals, biomechanical signals, bioacoustic signals and biooptical signals.
Nerve and muscle cells generate bioelectric signals that are the result of electrochemical changes within and between cells. When plenty of cells are stimulated, an electric field is then generated that propagates through biological tissues. These changes in extracellular potential may be measured on the surface of tissue or organism by using surface electrodes. The electrocardiogram (ECG) is an example of this phenomenon. Different organs in body, including the heart, brain, lungs, and liver, also generate weak magnetic fields that could be detected with magnetic sensors. The strength of magnetic field is much weaker than the corresponding physiological bioelectric signal. Magnetic sensors could be used to detect biomagnetic signals. Magnetocardiography (MCG) is a specific example of such phenomenon.
Biochemical signals contain information about changes in the concentration of various chemical agents in the body. The concentration of various ions such as calcium and potassium in cell can be measured and recorded. Oxygen sensor is used to detect oxygen concentration in body. Mechanical functions of biological systems, including motion, displacement, tension, force, pressure and flow, also produce measurable biological signals. Blood pressure sensor is a measurement of the force that blood exerts against the walls of blood vessels. Change in blood pressure can be recorded as a waveform by blood pressure sensor. Bioacoustics’ signals are a special subset of biochemical signals which involve vibrations. Many biological events could produce acoustic noise. For example, the flow of blood through the valves in the heart can be used to determine whether motion is operating properly. Besides these, the respiratory system, joints and muscles could also produce bioacoustic signals that propagate through the biological medium and can be often measured at the skin surface by acoustic sensors. Biooptical signals are generated by the optical or light induced attributes of biological systems. Biooptical signals can occur or be introduced to measure a biological parameter with an external light medium such as the measurement of health of a fetus by red and infrared light.
Noise
Measurement signals are always corrupted by noise in the bioinstrumentation system. Interference noise occurs when unwanted signals are introduced into systems by external sources such as telephone magnetic wave, power line and transmitted radio. Interference noise needs to be effectively reduced by careful attention to the circuit wiring configuration to minimize coupling effect.
Interference noise is introduced by power lines, fluorescent lights, AM/FM radio broadcasts, computer clock oscillator, laboratory equipment and cellphone. Electromagnetic energy radiating from noise source is injected into the amplifier circuit or into the patient by capacitive or inductive coupling. Even action potentials from nerve conduction in the patient generate noise at the sensor/amplifier surface. Filters are also used to reduce the noise and to maximize the signal-to-noise(S/N) rate at the input of the A/D converter.
Low frequency noise could be eliminated by high-pass filter with the cutoff frequency set above the noise frequency. High frequency noise could be reduced by low-pass filter with the cutoff frequency set below the noise frequency and above the frequency of biological signal which is being monitored. Power line noise is a very difficult problem in biological monitoring because the 50-or-60-Hz frequency is usually at the range of biological signal which could be monitored. Band-stop filters are commonly used to reduce the power line noise. The notch frequency in the band-stop filters is set to the power line frequency of 50 or 60Hz with the cutoff frequency located a few Hertz to either side.
The second type of noise is called inherent noise. Inherent noise arises from random processes that are fundamental to the operation of circuit’s elements and thus is reduced by a good circuit design practice. While inherent noise is reduced, it can be never eliminated. Low-pass filters are used to reduce high-frequency components. However, noise signals within the frequency range of biological signals being amplified cannot be eliminated by this filtering approach.
Computer
Computer is a main device which is used to display the biological signals being monitored. However some low or high level languages such as machine language, FORTRAN, visual C++, MATLAB or LabView, have to be used to realize the operation on the acquisition data from biological body. When computers are used to acquire physiological data, programming instruction tell computer when acquisition data should begin, how often samples should be taken from how many sensors, how long acquisition data should continue, and where the digitized data should be stored. The rate at which a system acquires sample depends on the speed of computer clock’s frequency and the number of computer instruction that could be completed in order to realize a sample. Of course, some computers are utilized to control the gain on the input amplifiers so that biological signals could be adjusted during data acquisition. In other systems, the gain of data acquisition has to be adjusted.
In this chapter, main biomedical sensors, devices and biological measurement systems are introduced to make readers understand present bioinstrumentation in market. The common biomedical sensors are narrated here to make readers grasp their basic sensing principle such as heart sound sensor, blood flow sensor and enzyme sensor. Furthermore, basic charge, current, voltage, power and energy used in biomedical engineering are explained to design some detecting circuits. Besides above, signal filters and operational amplifiers are also described and some advice or opinions are given out to give readers some available references. The basic detecting blocks of biomeasurement system are provided to quickly design relative bioinstrumentations. Readers need to carefully learn the content of biomedical sensors, signal filters, operational amplifiers for bioinstrumentation.
[1] Wang Baohua. Biomedical measurement and instrument [M]. China Fudan press, shanghai, January, 2009.
[2] Yang Yuxing. Biomedical sensor and measurement technology [M]. Beijing Chemical industry press, Beijing, 2005.
[3] John Enderle, Joseph Bronzino. Introduction to Biomedical Engineering [M]. Elsevier press, 2012.
Liver transplantation (LT) is the last resource for patients with end-stage liver failure. Currently, the excellent posttransplant survival rates shift the attention to improved patient care, quality of life, and diminishing posttransplant complications. LT can be performed with deceased donors or living donors. Also, the liver can be implanted as the hole organ, as in orthotopic liver transplantation (OLT) (Figure 1), or partial liver (left lobe, right lobe, left lateral segment) (Figure 2). Technical variant grafts include partial liver grafts from living donors, split liver, and reduced grafts and have historically been associated with higher risk of posttransplant vascular complications. The indications for LT and the techniques vary according to the age of the recipient, but basically involve a total liver resection with a graft implantation that requires three vascular anastomosis [hepatic vein (HV), portal vein (PV), and hepatic artery (HA)], and a biliary anastomosis. Each of the vascular anastomosis has a potential to suffer thrombosis and/or stenosis. The early diagnosis and intervention will determine the graft and patient survival, since any one of these may be fatal [1, 2].
Whole-liver transplant with related surgical anastomosis sites. 1= hepatic vein anastomosis using the recipients three hepatic veins and the common stump of the recipient hepatic veins by the piggyback technique; 2 = biliary anastomosis with choledochojejunostomy; 3 = HA reconstruction; and 4 = PV anastomosis [
Living-donor liver transplant, with left lateral liver graft with surgical anastomoses of the hepatic veins by using the piggyback technique (1), hepaticojejunostomy (2), HA reconstruction with two anastomoses (double HA technique) (3), and PV anastomosis (4) [
In the following paragraphs, a detailed review of the pathogenesis of each vascular complication and current available treatment options will be presented.
Hepatic vein anastomosis can be complicated by the development of stenosis and thrombosis. When venous drainage from the liver is compromised, liver parenchyma gets congested, causing impairment in the liver function, including a sluggish portal flow, and is called hepatic venous outflow obstruction (HVOO). Clinical manifestations of HVOO are nonspecific but may include abnormal liver function, hepatomegaly, ascites, pleural effusion, and lower-extremity edema. If it occurs in the immediate postoperative period, it can cause refractory graft dysfunction from liver congestion and graft loss. The mortality can be as high as 17–24% [3].
The incidence of HVOO after OLT varies from 0.5 to 9.5%. This incidence can be a little higher (3.9–16%) in living donor liver transplantation (LDLT) [4].
Routine Doppler ultrasound (DUS) performed in the immediate posttransplant period can identify signs of HVOO, such as dilated hepatic veins and dampened phasicity (pulsatility index less than 0.45) as lack of transmission of the right atrial waveform into the hepatic veins. In addition, the flow at the anastomosis often shows turbulence [5]. A computed tomography (CT) scan shows better sensitivity (97% vs. 87%) and specificity (86% vs. 68%) than DUS and allows the observation of parenchymal changes such as hypoattenuation during the portal venous phase or the delayed phase, which could suggest venous congestion [6]. The confirmation of this diagnosis is made by hepatic venography and manometry and is defined as stasis of the contrast medium from anastomotic obstruction on venography or a pressure gradient across the stenosis between the distal hepatic vein and the right atrium >5 mmHg. A pressure gradient of >5–6mmHg is widely accepted as the threshold for induction of symptoms [4].
Early complications (<30 days) are thought to be caused by technical factors such as a tight suture line, venous size match, kinking, and compression from a large graft. On the other hand, chronic (>30 days) obstructions are thought to result from fibrosis around the anastomotic site, intimal hyperplasia, twisting, or compression of the anastomosis from a hypertrophic graft [7].
Particular attention to anastomotic techniques is important such as performing a wide triangulated anastomosis, avoiding rotation of graft at the hepatocaval junction, and stabilization of the graft in an anatomical position [8]. Hepatic vein reconstruction is of particular challenge in right lobe grafts, in adult LDLT. Multiple middle hepatic vein tributaries draining the segment 5 vein (V5) are commonly found in donor hepatectomy using conventional modified right lobe grafts, leading to the performance of multiple anastomosis, including the use of vascular grafts to ensure adequate liver parenchymal drainage [4].
Treatment of HVOO depends on the time of presentation and the cause (Figure 3). Most patients can be managed by interventional radiology (IR), performing a balloon angioplasty, with or without stent placement (Figure 4). During the early postoperative period, given the mechanism of HVOO, there is a high chance of restenosis if angioplasty alone is done. Stent is therefore indicated, also because balloon dilatation carries a risk of anastomosis disruption in the first days. Primary stent placement may be an effective treatment modality with an acceptable long-term patency to manage early posttransplant HVOO. Jang et al reported a technical success rate of 96% and 3-year patency rate of 80% in 21 adult LDLT recipients with HVOO treated with IR [4].
Algorithm for the management of HVOO. HVOO: hepatic venous outflow obstruction; and IR: interventional radiology.
Hepatic vein stenosis treated with balloon angioplasty. (a) Left hepatic vein stenosis with evidence of collateral veins. (b) Trans-hepatic access and balloon positioning in the stenosis site. (c) Final aspect after balloon dilatation with resolution of collateral veins.
Surgical options should be considered if HVOO is evident at the initial operation, which can be assessed by a transoperative DUS or in the early postoperative period. Surgery is also preferred if there is thrombosis of the hepatic veins because of the high chance of pulmonary embolism with IR treatment [5]. Retransplantation is considered as a last resource, when recanalization fails after these previous attempts.
The incidence of portal vein complications (PVCs) varies according to the recipient (children vs. adult), the LT modality (LDLT vs. OLT), and the preexistence of portal vein thrombosis (PVT). Untreated, it can lead to retransplantation, which happens in almost half of the recipients with PVT [9, 10].
The incidence of PVT after OLT can be up to 3–7%, 4% after LDLT [10], and up to 30% in children [11]. LT in children can present with additional difficulties related to portal vein reconstruction (short vascular stumps, size discrepancy between the donor’s and the recipient’s vascular structures, anastomotic misalignment, stenosis, anastomotic kinks, low portal flow (<7 cm/s), small portal veins (<4 mm), and use of interposition vascular grafts) that can justify the higher incidence of portal vein complications [12].
The diagnosis of PVT can be made by the detection of clinical signs (fever, abdominal pain, intractable ascites, gastrointestinal bleeding, or encephalopathy) and/or laboratory abnormalities (elevated liver enzymes, elevated ammonia levels, and/or thrombocytopenia), or detected during routine posttransplant DUS examination. Some signs present in DUS can indicate a portal vein complication: decreased or absent PV blood flow, acceleration of blood flow at the PV anastomosis, and postanastomotic jet flow. Any of these findings should prompt a CT scan. A decrease in more than 50% in PV diameter in CT scan is a sign of portal vein stenosis (PVS) even though recipient/donor mismatch should always be considered in cases of LDLT and pediatric recipients. PVT appears in the CT scan as the absence of visible lumen at the site of a thrombus [10, 11, 12].
PVT can be classified into four grades according to Yerdel [13]: Grade I: thrombus at main PV affecting less than 50% of the lumen with or without minimal extension into superior mesenteric vein (SMV); Grade II: thrombus at PV affecting more than 50%, including complete thrombosis, with or without minimal extension into the SMV; Grade III: complete PVT plus thrombosis extending to the proximal SMV with patent distal SMV; Grade IV: complete PVT plus complete thrombosis of the SMV (proximal and distal).
Revascularization options for patients with PVT after LT will depend on the extension of the thrombosis and the time of onset/diagnosis. Surgical revision, systemic anticoagulation, catheter-based thrombolytic therapy, balloon angioplasty and stenting, portosystemic shunting compose the usual algorithm. Retransplantation remains as the last resource when everything else has failed [10].
Early complications (from 24 h to 1 week after LT) are usually associated with technical issues and tend to benefit from surgical revision (redo anastomosis, kinking, liver graft repositioning) (Figure 5). However, IR may play an important role as a salvage treatment when surgical revision of PV anastomoses fails. In contrast to early PVCs, late complications (>30 days), as well as grades 2–4 PVT, are associated with less favorable prognoses [11, 14].
Algorithm for the management of e-PVT. e-PVT: early portal vein thrombosis; LFT: liver function tests; and PV: portal vein.
Patients with grade 1 PVT without liver graft impairment can be treated with full heparinization [unfractioned or low-molecular-weight heparin (LMWH)] and then maintained anticoagulated with warfarin or rivaroxaban for 3–6 months. IR treatment is the first choice for patients with higher grades of PVT (2–4), portal vein occlusion, failed surgical revascularization, or failed recanalization with systemic anticoagulation (Figure 6). Balloon angioplasty with stent placement has high rates of success and low PVT recurrence [10, 11]. The PV access can be made percutaneously (trans-hepatic or trans-splenic) or via mini-laparotomy for a direct catheterization of the portal venous system through ileo-colic or mesenteric venous branches [10].
Algorithm for the management of late PVC. PVC: portal vein complication; PVS: portal vein stenosis; PVT: portal vein thrombosis; and IR: interventional radiology.
The trans-hepatic approach is usually chosen for the first attempt; however, in patients with chronic PVT, recanalization can be difficult, precluding venoplasty [15]. The ileo-colic approach involves a mini-laparotomy, followed by a catheterization of a venous branch, introduction of a 7 F sheath, and performance of the portography. This approach has advantages in terms of the certainty of portal catheterization [10]. Another option is the trans-splenic access, which is less injurious to the transplanted liver graft (Figure 7) [11].
Portal vein thrombosis treated with balloon angioplasty and stent. (a) Trans-splenic access and portography; (b) Passage of the guidewire through the site of thrombosis; (c) Balloon dilatation; and (d) Final aspect after stent positioning.
Despite the chosen access, IR protocols for PVT revascularization usually include catheterization, passage of the guidewire through the thrombosed segment, balloon angioplasty, and stent placement (Figure 7). A thrombolysis may be performed in order to facilitate the aspiration of the thrombus. The catheter is placed inside the thrombus and the thrombolytic agent infused. If the first treatment is considered ineffective, the catheter may be left and a continuous infusion of the thrombolytic agent maintained, from a period of 10 days to 30 days [10]. Patients are left anticoagulated after the procedure, at least for 3 months. Sanada et al. recommended the use of a three-agent anticoagulant therapy that combines low-molecular-weight heparin, warfarin, and aspirin for 3 months following balloon dilation for portal vein stenosis (PVS) in pediatric liver transplantation. Recurrence of PVS reduced from 55.6 to 0% in the long-term follow-up [16].
High rate of technical success can be achieved, and recent studies focus on LDLT. In adults, a rate of 80% was achieved with long-term patency in approximately 50–60% of cases [10]. Cavalcante et al reported on pediatric LDLT recipients with chronic PVT who underwent IR with stent placement using a trans-mesenteric approach. The technical success was of 78.6%; and 31.8% developed restenosis/thrombosis and attempted a new dilatation via transhepatic access. Most of the patients (78.5%) had less than 1 year of PVT, with an 81.8% technical success rate in this group, compared with a rate of 66.7% in patients with more than 1 year of PVT [11].
In cases of PVS, balloon angioplasty is considered the first line of treatment and has produced highly successful results (Figure 8). However, 28–50% of these patients may develop recurrent stenosis. There is no minimal time one should wait to perform an angioplasty, even though some groups are concerned about the risk of rupture of the suture. Some cases of PVS induced by chronic PVT are not resolved with balloon angioplasty, because the wall flexibility induces easy expansion and reversion of the PV wall by inflation and deflation of the balloon. Stent placement benefits these cases [10].
Portal vein stenosis treated with balloon angioplasty. (a) Trans-hepatic access and portography; (b) Passage of the guidewire through the site of stenosis; (c) Balloon dilatation; and (d) Final aspect.
Early detection and treatment of PVS or PVT are paramount to avoid portal vein occlusion. Occluded PV has a low success of stent placement. After 1 year of PVT, chances can be as low as 0% [17]. The treatment of a completely occluded PV is directed to the management of portal hypertension, which includes medical treatment, shunt surgery (portosystemic shunt or meso-Rex shunt), and ultimately, retransplantation (Figure 6) [18].
Hepatic artery complications can be classified into thrombosis and stenosis. Acute complications can be represented by early hepatic artery thrombosis (e-HAT), and chronic complications are related to late hepatic artery thrombosis (l-HAT) and hepatic artery stenosis (HAS). Revascularization strategies for these situations include surgical thrombectomy, endovascular thrombectomy, endovascular thrombolysis, systemic anticoagulation, systemic thrombolysis, and endovascular angioplasty and stent placement. The pathogenesis and best treatment modality of each type of complication will be discussed.
e-HAT presents early in the posttransplant course. There is lack of definition in the literature about the post-LT period in which e-HAT should be classified, some assume 14 days, some 30 days, or even as long as 100 days. It can present asymptomatically and be detected with routine posttransplant DUS, but if left untreated can lead to liver failure and retransplantation. e-HAT has been associated with high mortality rate after LT, around 33% [19].
The incidence varies according to the transplant center, the age of the recipient, the transplant modality, and surgical technique. During the initial experience, rates in children reached 42% and 12% in adult recipients. More recently, the combined reported incidence of e-HAT dropped to 4.4%, and to 1–20% in pediatric recipients. Factors such as the surgical learning curve, development of microsurgical techniques, and the routine use of magnifying lenses during arterial anastomosis are responsible for these improvements. The higher incidence reported in children can be in part explained by the smaller vessels, raising the difficulty of the anastomosis. Centers that have adopted microsurgical technique have in fact reported a low incidence of e-HAT, even with partial grafts, as is the case in LDLT [2, 20]. A study by Li et al., in the setting of adult living donor liver transplantation, reported an incidence of 1.8% of HA complications using magnifying loups instead of the microscope [21].
e-HAT can be associated to surgical technique or intraoperative positioning of the hepatic artery (kinking), and when diagnosed in the first 24h after LT, surgical reintervention to check the position of the hepatic artery, check patency, or even redo the anastomosis is the best approach (Figure 9). Other nonsurgical causes of e-HAT include the development of slow arterial flow during an episode of acute rejection, patient hypercoagulability, cytomegalovirus infection, and immunization status, among others. A cytomegalovirus(CMV) recipient/donor mismatch emerged as a concordant risk factor. Patients submitted to a retransplantation are also in an increased risk of e-HAT [19, 20].
Algorithm for the management of early hepatic artery thrombosis (e-HAT).
Since symptoms are absent during the first hours after e-HAT, routine DUS is paramount to diagnose and immediately treat this complication. Measuring the resistive index is performed as part of the DUS evaluation. A normal resistive index value ranges between 0.60 and 0.80, and values less than 0.50 have been shown to diagnosis HAS or thrombosis with a sensitivity 60% and specificity 77%. Ultrasound can detect up to 90% of all cases of HAT, but false positives can be seen in the setting of hepatic edema, systemic hypotension, or technical aspects limiting the study. CT scan has the advantage of being rapid, not operator-dependent, provides high spatial resolution of small vessels, and gives a superior anatomical overview with the aid of contrast. The combination of absent flow on DUS with confirmation on CT scan is commonly acceptable for the diagnosis of HAT. Other signs such as elevation of liver enzymes, compromise in liver function may be absent, specifically in the setting of LDLT, where the quality of the liver graft masks this alterations [2, 22, 23].
If HAT is unrecognized, the fate of the liver graft will depend on the potential for and the efficiency of developing a collateral arterial circulation and supervening infection within the compromised biliary tree. Untreated, this can progress to liver failure and death [24].
Interventions for e-HAT include urgent revascularization with thrombectomy, vascular anastomosis revision, and thrombolytic drug therapy. Traditionally, the choice was urgent retransplantation or conservative management. Most centers employ a combination of these interventions. There are no randomized controlled data to guide management. Reported studies often lack clear information about graft and patient outcomes and the selection criteria for treatment [24].
Although retransplant has been the first choice of therapy, it is associated with higher morbidity than primary transplant. Surgical options for acute HAT have traditionally included surgical revascularization and open thrombectomy. With major advancements in technology, endovascular management has emerged as a less invasive alternative treatment option.
A revascularization attempt is performed in approximately half of the cases of e-HAT, with a reported success rate of about 50% [20]. Surgical revascularization can be attempted in the first 24h after the diagnosis an e-HAT. Accerman et al performed urgent surgical revascularization in 31 children with diagnosed HAT after LT. Interventions included thrombectomy, with or without fibrinolysis, creation of a new anastomosis and conduit interposition. Success rates were reported in 61% of the cases [25]. Children are more likely than adults to have a successful outcome after early revascularization (61% of adults and 92% of children) [20, 26].
In the study of Pannaro et al., e-HAT required surgical revision in 77% patients and retransplant in 15.4%. Of the patients that required surgical revision, thrombectomy was performed in the majority and few required hepatic artery anastomotic revision. The graft salvage rate for this group was 80% [27].
In case of failed surgical revascularization, thrombolysis can still be pursued, either locally through endovascular therapy or systemically, as recently reported by our group. Systemic alteplase as a rescue therapy salvaged liver grafts in two children with e-HAT [23].
Late HAT manifesting months or years after surgery may be asymptomatic or have an insidious course characterized by cholangitis, relapsing fever, and bacteremia. The pathognomonic sign of HAT is the development of nonanastomotic/complex biliary stricture, most commonly at the hilum. The formation of bile casts and duct ischemia predispose the patient to recurrent cholangitis and obstructions with the development of biliary abscesses and liver infarction [2, 20, 28].
Some patients presenting l-HAT develop a neovascularized liver. Even though these patients are prone to develop biliary complications, they are treated with repeated bile duct drainage procedures (endoscopic and/or radiological), and the graft salvage rate can reach 100% [27]. Factors influencing the likelihood of spontaneous, effective collateral formation are poorly understood but include the site of the arterial thrombosis (closer to the hilum), the graft type (split/reduced grafts), Roux-en-Y hepaticojejunostomy, multiple arteries, and the timing after LT [24].
HAS is an insidious vascular complication occurring after LT. The most common complication seen in patients with HAS is biliary strictures. HAS usually occurs at or near the anastomosis site as a result of operative technique. The reported HAS rate after LT ranges from 5 to 11% [21].
HAS can be suspected when DUS presents a tardus parvus waveform (defined as a waveform with a resistive index < 0.5 and a systolic acceleration time <0.08 seconds), but has a low positive predictive value and a high false-positive rate. CT scan is indicated to confirm the diagnosis, and arteriography can be used both as a diagnostic and a treatment option [24]. Treatment options for HAS shifted from surgical reintervention to IR balloon angioplasty, with or without stent placement (Figure 10) [27].
Hepatic artery stenosis treated with balloon angioplasty. (a) Arteriography demonstrating the hepatic artery originating from the superior mesenteric artery and the stenosis (arrow); and (b) Final aspect after balloon dilatation.
Patients treated with a transluminal radiological intervention can expect a patency rate >90% within 5 years. Repeat interventions may be performed in case of HAS recurrence. Angioplasty is useful in treatment of first-time stenosis, with stenting reserved for resistant stenosis [29].
HAT has been reported to be successfully treated with multiple endovascular techniques, including transcatheter intra-arterial thrombolysis (IAT), percutaneous transluminal angioplasty (PTA), stenting, or a combination of these [29]. Selective thrombolysis via the hepatic artery, IAT, has several advantages such as small thrombolytic dose, high localized concentration, and little influence on systemic coagulation. It is thought to be safe and effective if the infusion catheter is placed inside the thrombus. Despite its local effect, hemorrhage is the most common complication of IAT.
Urokinase (UK) and alteplase (t-PA) are the most common thrombolytic agents used, with no documented advantage of one over the other. Thrombolytic agents (plasminogen activators) convert plasminogen into plasmin, which further cleaves the fibrin strands within the thrombus, leading to clot dissolution. t-PA is a more potent activator of plasminogen and has higher affinity for fibrin within the clot. Thrombolytic agents can be infused in spaced doses [19] or continuously [30]. The lowest effective dosage and duration have not yet been determined. Dosages can vary from 1 to 3 mg (t-PA) or from 50,000 to 250,000 IU (UK) [31]. Continuous infusion can be maintained for 2–4 days with different dosing regimens, using up to 9 million units of UK [32]. Intra-arterial thrombolysis should be terminated if there is residual thrombus or persistent HAT after 36–48 h of thrombolytic therapy [33]. The estimated success rate of thrombolysis is of 68% [19].
Careful monitoring of coagulation profile and clinical symptoms is necessary during thrombolysis treatment. Fibrinogen levels should be kept above 100 mg/dl [34]; however, there is no evidence to support that fibrinogen levels are predictive of adverse bleeding; as hemorrhagic complications can also occur with values above 100 mg/dl. If adverse bleeding occurs, thrombolytic agent should be immediately terminated, and any other cause for bleeding should be addressed.
IAT can reveal other reasons for HAT, including kinking, anastomotic stenosis, or stricture, which if left untreated can lead to rethrombosis. The combined use of thrombolysis with PTA and/or stenting has been shown to have better patency and survival rates than thrombolysis alone. Angioplasty is useful in treatment of first-time stenosis, with stenting reserved for resistant stenosis [35].
Medical management without surgical or endovascular intervention has yet to be confirmed as an effective treatment option for HAT. Our group recently published the successful outcome with the multimodal treatment for e-HAT after pediatric LT. Two children were successfully rescued with systemic t-PA and heparinization [23].
Posttransplant anticoagulation, even with LMWH as part of the protocol, has been shown to reduce the incidence of HAT, but does not lead to resolution (31, 32). Our posttransplant protocol includes prophylactic heparin when TTPA < 2.5 times control, and aspirin 3mg/kg when the patient resumes oral intake and platelets are >100.000. DUS is performed during the LT, in the first 24h after the transplant, and subsequently according to clinical judgment.
Systemic heparinization can salvage a liver graft after HAT if the patient has a neovascularized liver or if there is HA recanalization, which occurs less frequently. The complete understanding of how systemic heparinization or systemic thrombolysis can actually prevent retransplantation is still under debate [23, 27]. However, it is a valuable salvage therapy for these patients, and one should not hesitate in administering even if the patients go to a retransplant waiting list.
Posttransplant vascular complications jeopardize the liver graft and can impact on graft and patient survival. An impeccable surgical technique, along with close posttransplant surveillance to ensure an early diagnosis and prompt treatment, will enhance the chances to avoid retransplantation. It was not until recently that IR and thrombolysis have replaced retransplantation as the first treatment choice. Complications occurring <24 h after the LT are still best managed with surgical revision, because technical issues are usually responsible and can be addressed. Later occurring complications, however, are best managed nonoperatively, with high success rates for current therapies. Retransplantation is reserved as last resource when previous attempts have failed or when the liver grafts are already beyond salvation.
This article was funded by Teaching and Research Institute of Hospital Santa Casa de Porto Alegre, Porto Alegre, Brazil.
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These social responsibilities of the engineering profession are in many ways synonymous with macroethics. Analysis of the engineering codes of ethics and educational requirements are used to support these arguments, and are compared with the perceptions of engineering students and working engineers. The social responsibilities of engineers include human safety and environmental protection in engineering designs. But it may extend further to include pro bono work and considerations of social justice issues. Research has found that perceptions of the professional social responsibilities of engineers vary across different countries/cultures, engineering disciplines (e.g., mechanical versus environmental engineers) and by gender. The impact of engineering education and broader college experiences on evolving notions of professional social responsibility will be described, in particular community engagement. 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Among the inequalities that impede the social cohesion of a country, gender inequality is of paramount importance, affecting more than half of the population. Based on the concept of Horizontal Inequality (HI) the chapter analyzes discrimination against women in three population groups comprising the 125.5 million Mexican society: 23 million Indigenous population, the 2.5 Afro-descendant population and the 101 million remaining. Horizontal Inequality explains discrimination for reasons of ethnicity, gender, religion, and language, among others identity facts that are not of free decision and from which there is no group way out. Only individuals can escape from discrimination. It is expressed in different areas of social activity such as politics, economics, justice, social services and culture. 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