Medical ultrasound includes diagnostic techniques (mainly imaging techniques) using ultrasound, as well as therapeutic applications of ultrasound. In diagnosis, it is used to create an image of internal body structures such as tendons, muscles, joints, blood vessels, and internal organs, to measure some characteristics (e.g. distances and velocities) or to generate an informative audible sound. Its aim is usually to find a source of disease or to exclude pathology. The usage of ultrasound to produce visual images for medicine is called medical ultrasonography or simply sonography. The practice of examining pregnant women using ultrasound is called obstetric ultrasonography, and was an early development of clinical ultrasonography.
Ultrasound is composed of sound waves with frequencies which are significantly higher than the range of human hearing (>20,000 Hz). Ultrasonic images, also known as sonograms, are created by sending pulses of ultrasound into tissue using a probe. The ultrasound pulses echo off tissues with different reflection properties and are returned to the probe which records and displays them as an image.
Many different types of images can be formed. The most common is a B-mode image (Brightness), which displays the acoustic impedance of a two-dimensional cross-section of tissue. Other types display blood flow, motion of tissue over time, the location of blood, the presence of specific molecules, the stiffness of tissue, or the anatomy of a three-dimensional region.
Compared to other medical imaging modalities, ultrasound has several advantages. It provides images in real-time, is portable, and can consequently be brought to the bedside. It is substantially lower in cost than other imaging strategies and does not use harmful ionizing radiation. Drawbacks include various limits on its field of view, the need for patient cooperation, dependence on patient physique, difficulty imaging structures obscured by bone, air or gases,[note 1] and the necessity of a skilled operator, usually with professional training.
Sonography (ultrasonography) is widely used in medicine. It is possible to perform both diagnosis and therapeutic procedures, using ultrasound to guide interventional procedures such as biopsies or to drain collections of fluid, which can be both diagnostic and therapeutic. Sonographers are medical professionals who perform scans which are traditionally interpreted by radiologists, physicians who specialize in the application and interpretation of medical imaging modalities, or by cardiologists in the case of cardiac ultrasonography (echocardiography). Increasingly, physicians and other healthcare professionals who provide direct patient care are using ultrasound in office and hospital practice (point-of-care ultrasound).
Sonography is effective for imaging soft tissues of the body. Superficial structures such as muscle, tendon, testis, breast, thyroid and parathyroid glands, and the neonatal brain are imaged at higher frequencies (7–18 MHz), which provide better linear (axial) and horizontal (lateral) resolution. Deeper structures such as liver and kidney are imaged at lower frequencies (1–6 MHz) with lower axial and lateral resolution as a price of deeper tissue penetration.
A general-purpose ultrasound transducer may be used for most imaging purposes but some situations may require the use of a specialized transducer. Most ultrasound examination is done using a transducer on the surface of the body, but improved visualization is often possible if a transducer can be placed inside the body. For this purpose, special-use transducers, including endovaginal, endorectal, and transesophageal transducers are commonly employed. At the extreme, very small transducers can be mounted on small diameter catheters and placed within blood vessels to image the walls and disease of those vessels.
In anesthesiology, ultrasound is commonly used to guide the placement of needles when injecting local anaesthetic solutions in the proximity of nerves identified within the ultrasound image (nerve block). It is also used for vascular access such as cannulation of large central veins and for difficult arterial cannulation. Transcranial Doppler is frequently used by neuro-anesthesiologists for obtaining information about flow-velocity in the basal cerebral vessels.
In angiology or vascular medicine, duplex ultrasound (B Mode imaging combined with Doppler flow measurement) is used to diagnose arterial and venous disease. This is particularly important in potential neurologic problems, where carotid ultrasound is commonly used for assessing blood flow and potential or suspected stenoses in the carotid arteries, while transcranial Doppler is used for imaging flow in the intracerebral arteries.
Intravascular ultrasound (IVUS) uses a specially designed catheter with a miniaturized ultrasound probe attached to its distal end, which is then threaded inside a blood vessel. The proximal end of the catheter is attached to computerized ultrasound equipment and allows the application of ultrasound technology, such as a piezoelectric transducer or capacitive micromachined ultrasonic transducer, to visualize the endothelium of blood vessels in living individuals.
In the case of the common and potentially, serious problem of blood clots in the deep veins of the leg, ultrasound plays a key diagnostic role, while ultrasonography of chronic venous insufficiency of the legs focuses on more superficial veins to assist with planning of suitable interventions to relieve symptoms or improve cosmetics.
Echocardiography is an essential tool in cardiology, assisting in evaluation of heart valve function, such as stenosis or insufficiency, strength of cardiac muscle contraction, and hypertrophy or dilatation of the main chambers. (ventricle and atrium)
Point of care ultrasound has many applications in emergency medicine. These include differentiating cardiac from pulmonary causes of acute breathlessness, and the Focused Assessment with Sonography for Trauma (FAST) exam, extended to include assessment for significant hemoperitoneum or pericardial tamponade after trauma (EFAST). Other uses include assisting with differentiating causes of abdominal pain such as gallstones and kidney stones. Emergency Medicine Residency Programs have a substantial history of promoting the use of bedside ultrasound during physician training.
Both abdominal and endoanal ultrasound are frequently used in gastroenterology and colorectal surgery. In abdominal sonography, the major organs of the abdomen such as the pancreas, aorta, inferior vena cava, liver, gall bladder, bile ducts, kidneys, and spleen may be imaged. However, sound waves may be blocked by gas in the bowel and attenuated to differing degrees by fat, sometimes limiting diagnostic capabilities. The appendix can sometimes be seen when inflamed (e.g.: appendicitis) and ultrasound is the initial imaging choice, avoiding radiation if possible, although it frequently needs to be followed by other imaging methods such as CT. Endoanal ultrasound is used particularly in the investigation of anorectal symptoms such as fecal incontinence or obstructed defecation. It images the immediate perianal anatomy and is able to detect occult defects such as tearing of the anal sphincter. Ultrasonography of liver tumors allows for both detection and characterization.
Gynecology and obstetrics
Gynecologic ultrasonography examines female pelvic organs (specifically the uterus, ovaries, and Fallopian tubes) as well as the bladder, adnexa, and Pouch of Douglas. It uses transducers designed for approaches through the lower abdominal wall, curvilinear and sector, and specialty transducers such as endovaginal.
Obstetrical sonography was originally developed in the late 1950s and 1960s by Sir Ian Donald and is commonly used during pregnancy to check the development and presentation of the fetus. It can be used to identify many conditions that could be potentially harmful to the mother and/or baby possibly remaining undiagnosed or with delayed diagnosis in the absence of sonography. It is currently believed that the risk of delayed diagnosis is greater than the small risk, if any, associated with undergoing an ultrasound scan. However, its use for non-medical purposes such as fetal "keepsake" videos and photos is discouraged.
Obstetric ultrasound is primarily used to:
- Date the pregnancy (gestational age)
- Confirm fetal viability
- Determine location of fetus, intrauterine vs ectopic
- Check the location of the placenta in relation to the cervix
- Check for the number of fetuses (multiple pregnancy)
- Check for major physical abnormalities.
- Assess fetal growth (for evidence of intrauterine growth restriction (IUGR))
- Check for fetal movement and heartbeat.
- Determine the sex of the baby
According to the European Committee of Medical Ultrasound Safety (ECMUS)
Ultrasonic examinations should only be performed by competent personnel who are trained and updated in safety matters. Ultrasound produces heating, pressure changes and mechanical disturbances in tissue. Diagnostic levels of ultrasound can produce temperature rises that are hazardous to sensitive organs and the embryo/fetus. Biological effects of non-thermal origin have been reported in animals but, to date, no such effects have been demonstrated in humans, except when a micro-bubble contrast agent is present.
Nonetheless, care should be taken to use low power settings and avoid pulsed wave scanning of the fetal brain unless specifically indicated in high risk pregnancies.
Figures released for the period 2005–2006 by the UK Government (Department of Health) show that non-obstetric ultrasound examinations constituted more than 65% of the total number of ultrasound scans conducted.
Hemodynamics (blood circulation)
Blood velocity can be measured in various blood vessels, such as middle cerebral artery or descending aorta, by relatively inexpensive and low risk ultrasound Doppler probes attached to portable monitors. These provide non-invasive or transcutaneous (non-piercing) minimal invasive blood flow assessment. Common examples are, Transcranial Doppler, Esophogeal Doppler and Suprasternal Doppler.
Otolaryngology (head and neck)
Most structures of the neck, including the thyroid and parathyroid glands, lymph nodes, and salivary glands, are well-visualized by high-frequency ultrasound with exceptional anatomic detail. Ultrasound is the preferred imaging modality for thyroid tumors and lesions, and its use is important in the evaluation, preoperative planning, and postoperative surveillance of patients with thyroid cancer. Many other benign and malignant conditions in the head and neck can be differentiated, evaluated, and managed with the help of diagnostic ultrasound and ultrasound-guided procedures.
In neonatology, transcranial Doppler can be used for basic assessment of intracerebral structural abnormalities, suspected hemorrhage, ventriculomegaly or hydrocephalus and anoxic insults (Periventricular leukomalacia). It can be performed through the soft spots in the skull of a newborn infant (Fontanelle) until these completely close at about 1 year of age by which time they have formed a virtually impenetrable acoustic barrier to ultrasound. The most common site for cranial ultrasound is the anterior fontanelle. The smaller the fontanelle, the more the image is compromised.
- A-scan ultrasound biometry, is commonly referred to as an A-scan (Amplitude scan). A-mode provides data on the length of the eye, which is a major determinant in common sight disorders, especially for determining the power of an intraocular lens after cataract extraction.
- B-scan ultrasonography, or B-scan, is a B-mode scan that produces a cross-sectional view of the eye and the orbit. Its use in the emergency department for the timely diagnosis of conditions such as retinal or vitreous detachment, retinal and vitreous hemorrhages, and intra-ocular foreign bodies is common and important.
Ultrasound is used to assess the lungs in a variety of settings including critical care, emergency medicine, trauma surgery, as well as general medicine. This imaging modality is used at the bedside or examination table to evaluate a number of different lung abnormalities as well as to guide procedures such as thoracentesis, (drainage of pleural fluid (effusion)), needle aspiration biopsy, and catheter placement. Although air present in the lungs does not allow good penetration of ultrasound waves, interpretation of specific artifacts created on the lung surface can be used to detect abnormalities.
Lung ultrasound basics
- The Normal Lung Surface: The lung surface is composed of visceral and parietal pleura. These two surfaces are typically pushed together and make up the pleural line, which is the basis of lung (or pleural) ultrasound. This line is visible less than a centimeter below the rib line in most adults. On ultrasound, it is visualized as a hyperechoic (bright white) horizontal line if the ultrasound probe is applied perpendicularly to the skin.
- Artifacts: Lung ultrasound relies on artifacts, which would otherwise be considered a hindrance in imaging. Air blocks the ultrasound beam and thus visualizing healthy lung tissue itself with this mode of imaging is not practical. Consequently, physicians and sonographers have learned to recognize patterns that ultrasound beams create when imaging healthy versus diseased lung tissue. Three commonly seen and utilized artifacts in lung ultrasound include lung sliding, A-lines, and B-lines.
- § Lung Sliding: The presence of lung sliding, which indicates the shimmering of the pleural line that occurs with movement of the visceral and parietal pleura against one another with respiration (sometimes described as 'ants marching'), is the most important finding in normal aerated lung. Lung sliding indicates both that the lung is present at the chest wall and that the lung is functioning.
- § A-lines: When the ultrasound beam makes contact with the pleural line, it is reflected back creating a bright white horizontal line. The subsequent reverberation artifacts that appear as equally spaced horizontal lines deep to the pleura are A-lines. Ultimately, A-lines are a reflection of the ultrasound beam from the pleura with the space between A-lines corresponding to the distance between the parietal pleura and the skin surface. A-lines indicate the presence of air, which means that these artifacts can be present in normal healthy lung (and also in patients with pneumothorax).
- § B-lines: B-lines are also reverberation artifacts. They are visualized as hyperechoic vertical lines extending from the pleura to the edge of the ultrasound screen. These lines are sharply defined and laser-like and typically do not fade as they progress down the screen. A few B-lines that move along with the sliding pleura can be seen in normal lung due to acoustic impedance differences between water and air. However, excessive B-lines (three or more) are abnormal and are typically indicative of underlying lung pathology.
Lung pathology assessed with ultrasound
- Pulmonary edema: Lung ultrasound has been shown to be very sensitive for the detection of pulmonary edema. It allows for improvement in diagnosis and management of critically ill patients, particularly when used in combination with echocardiography. The sonographic feature that is present in pulmonary edema is multiple B-lines. B-lines can occur in a healthy lung; however, the presence of 3 or more in the anterior or lateral lung regions is always abnormal. In pulmonary edema, B-lines indicate an increase in the amount of water contained in the lungs outside of the pulmonary vasculature. B-lines can also be present in a number of other conditions including pneumonia, pulmonary contusion, and lung infarction. Additionally, it is important to note that there are multiple types of interactions between the pleural surface and the ultrasound wave that can generate artifacts with some similarity to B-lines but which do not have pathologic significance.
- Pneumothorax: In clinical settings when pneumothorax is suspected, lung ultrasound can aid in diagnosis. In pneumothorax, air is present between the two layers of the pleura and lung sliding on ultrasound is therefore absent. The negative predictive value for lung sliding on ultrasound is reported as 99.2–100% - briefly, if lung sliding is present, a pneumothorax is effectively ruled out. The absence of lung sliding, however, is not necessarily specific for pneumothorax as there are other conditions that also cause this finding including acute respiratory distress syndrome, lung consolidations, pleural adhesions, and pulmonary fibrosis.
- Pleural effusion: Lung ultrasound is a cost-effective, safe, and non-invasive imaging method that can aid in the prompt visualization and diagnosis of pleural effusions. Effusions can be diagnosed by a combination of physical exam, percussion, and auscultation of the chest. However, these exam techniques can be complicated by a variety of factors including the presence of mechanical ventilation, obesity, or patient positioning, all of which reduce the sensitivity of the physical exam. Consequently, lung ultrasound can be an additional tool to augment plain chest Xray and chest CT. Pleural effusions on ultrasound appear as structural images within the thorax rather than an artifact. They will typically have four distinct borders including the pleural line, two rib shadows, and a deep border. In critically ill patients with pleural effusion, ultrasound may guide procedures including needle insertion, thoracentesis, and chest-tube insertion.
- Lung cancer staging: In pulmonology, endobronchial ultrasound (EBUS) probes are applied to standard flexible endoscopic probes and used by pulmonologists to allow for direct visualization of endobronchial lesions and lymph nodes prior to transbronchial needle aspiration. Among its many uses, EBUS aids in lung cancer staging by allowing for lymph node sampling without the need for major surgery.
- COVID-19: Lung ultrasound has proved useful in the diagnosis of COVID-19 especially in cases where other investigations are not available.
Ultrasound is routinely used in urology to determine the amount of fluid retained in a patient's bladder. In a pelvic sonogram, images include the uterus and ovaries or urinary bladder in females. In males, a sonogram will provide information about the bladder, prostate, or testicles (for example to urgently distinguish epididymitis from testicular torsion). In young males, it is used to distinguish more benign testicular masses (varicocele or hydrocele) from testicular cancer, which is curable but must be treated to preserve health and fertility. There are two methods of performing pelvic sonography – externally or internally. The internal pelvic sonogram is performed either transvaginally (in a woman) or transrectally (in a man). Sonographic imaging of the pelvic floor can produce important diagnostic information regarding the precise relationship of abnormal structures with other pelvic organs and it represents a useful hint to treat patients with symptoms related to pelvic prolapse, double incontinence and obstructed defecation. It is also used to diagnose and, at higher frequencies, to treat (break up) kidney stones or kidney crystals (nephrolithiasis).
Penis and scrotum
Musculoskeletal ultrasound is used to examine tendons, muscles, nerves, ligaments, soft tissue masses, and bone surfaces. It is helpful in diagnosing ligament sprains, muscles strains and joint pathology. It is an alternative or supplement to x-ray imaging in detecting fractures of the wrist, elbow and shoulder for patients up to 12 years (Fracture sonography).
Quantitative ultrasound is an adjunct musculoskeletal test for myopathic disease in children; estimates of lean body mass in adults; proxy measures of muscle quality (i.e., tissue composition) in older adults with sarcopenia
In nephrology, ultrasonography of the kidneys is essential in the diagnosis and management of kidney-related diseases. The kidneys are easily examined, and most pathological changes are distinguishable with ultrasound. It is an accessible, versatile, relatively economic, and fast aid for decision-making in patients with renal symptoms and for guidance in renal intervention. Using B-mode imaging, assessment of renal anatomy is easily performed, and US is often used as image guidance for renal interventions. Furthermore, novel applications in renal US have been introduced with contrast-enhanced ultrasound (CEUS), elastography and fusion imaging. However, renal US has certain limitations, and other modalities, such as CT (CECT) and MRI, should be considered for supplementary imaging in assessing renal disease.
Intravenous access, for the collection of blood samples to assist in diagnosis or laboratory investigation including blood culture, or for administration of intravenous fluids for fluid maintenance of replacement or blood transfusion in sicker patients, is a common medical procedure. The need for intravenous access occurs in the outpatient laboratory, in the inpatient hospital units, and most critically in the Emergency Room and Intensive Care Unit. In many situations, intravenous access may be required repeatedly or over a significant time period. In these latter circumstances, a needle with an overlying catheter is introduced into the vein and the catheter is then inserted securely into the vein while the needle is withdrawn. The chosen veins are most frequently selected from the arm, but in challenging situations, a deeper vein from the neck (external jugular vein) or upper arm (subclavian vein) may need to be used. There are many reasons why the selection of a suitable vein may be problematic. These include, but are not limited to, obesity, previous injury to veins from inflammatory reaction to previous ‘blood draws’, previous injury to veins from recreational drug use.
In these challenging situations, the insertion of a catheter into a vein has been greatly assisted by the use of ultrasound. The ultrasound unit may be ‘cart-based’ or ‘handheld’ using a linear transducer with a frequency of 10 to 15 megahertz. In most circumstances, choice of vein will be limited by the requirement that the vein is within 1.5 cms. from the skin surface. The transducer may be placed longitudinally or transversely over the chosen vein. Ultrasound training for intravenous cannulation is offered in most ultrasound training programs.
From sound to image
Producing a sound wave
A sound wave is typically produced by a piezoelectric transducer encased in a plastic housing. Strong, short electrical pulses from the ultrasound machine drive the transducer at the desired frequency. The frequencies can vary between 1 and 18 MHz, though frequencies up to 50–100 megahertz have been used experimentally in a technique known as biomicroscopy in special regions, such as the anterior chamber of the eye.
Older technology transducers focused their beam with physical lenses. Contemporary technology transducers use digital antenna array techniques (piezoelectric elements in the transducer produce echos at different times) to enable the ultrasound machine to change the direction and depth of focus. As stated, the sound is focused either by the shape of the transducer, a lens in front of the transducer, or a complex set of control pulses from the ultrasound scanner, in the beamforming or spatial filtering technique. This focusing produces an arc-shaped sound wave from the face of the transducer. The wave travels into the body and comes into focus at a desired depth.
Materials on the face of the transducer enable the sound to be transmitted efficiently into the body (often a rubbery coating, a form of impedance matching). In addition, a water-based gel is placed between the patient's skin and the probe to facilitate ultrasound transmission into the body. This is because air causes total reflection of ultrasound; impeding the transmission of ultrasound into the body.
The sound wave is partially reflected from the layers between different tissues or scattered from smaller structures. Specifically, sound is reflected anywhere where there are acoustic impedance changes in the body: e.g. blood cells in blood plasma, small structures in organs, etc. Some of the reflections return to the transducer.
Receiving the echoes
The return of the sound wave to the transducer results in the same process as sending the sound wave, in reverse. The returned sound wave vibrates the transducer and the transducer turns the vibrations into electrical pulses that travel to the ultrasonic scanner where they are processed and transformed into a digital image.
Forming the image
To make an image, the ultrasound scanner must determine two characteristics from each received echo:
- How long it took the echo to be received from when the sound was transmitted. (Time and distance are equivalent.)
- How strong the echo was.
Once the ultrasonic scanner determines these two, it can locate which pixel in the image to illuminate and with what intensity.
Transforming the received signal into a digital image may be explained by using a blank spreadsheet as an analogy. First picture a long, flat transducer at the top of the sheet. Send pulses down the 'columns' of the spreadsheet (A, B, C, etc.). Listen at each column for any return echoes. When an echo is heard, note how long it took for the echo to return. The longer the wait, the deeper the row (1,2,3, etc.). The strength of the echo determines the brightness setting for that cell (white for a strong echo, black for a weak echo, and varying shades of grey for everything in between.) When all the echoes are recorded on the sheet, a greyscale image has been accomplished.
Displaying the image
Images from the ultrasound scanner are transferred and displayed using the DICOM standard. Normally, very little post processing is applied.
Sound in the body
Ultrasonography (sonography) uses a probe containing multiple acoustic transducers to send pulses of sound into a material. Whenever a sound wave encounters a material with a different density (acoustical impedance), some of the sound wave is scattered but part is reflected back to the probe and is detected as an echo. The time it takes for the echo to travel back to the probe is measured and used to calculate the depth of the tissue interface causing the echo. The greater the difference between acoustic impedances, the larger the echo is. If the pulse hits gases or solids, the density difference is so great that most of the acoustic energy is reflected and it becomes impossible to progress further.
The frequencies used for medical imaging are generally in the range of 1 to 18 MHz. Higher frequencies have a correspondingly smaller wavelength, and can be used to make more detailed sonograms. However, the attenuation of the sound wave is increased at higher frequencies, so penetration of deeper tissues necessitates a lower frequency (3–5 MHz).
Penetrating deep into the body with sonography is difficult. Some acoustic energy is lost each time an echo is formed, but most of it (approximately ) is lost from acoustic absorption. (See Acoustic attenuation for further details on modeling of acoustic attenuation and absorption.)
The speed of sound varies as it travels through different materials, and is dependent on the acoustical impedance of the material. However, the sonographic instrument assumes that the acoustic velocity is constant at 1540 m/s. An effect of this assumption is that in a real body with non-uniform tissues, the beam becomes somewhat de-focused and image resolution is reduced.
To generate a 2-D image, the ultrasonic beam is swept. A transducer may be swept mechanically by rotating or swinging or a 1-D phased array transducer may be used to sweep the beam electronically. The received data is processed and used to construct the image. The image is then a 2-D representation of the slice into the body.
3-D images can be generated by acquiring a series of adjacent 2-D images. Commonly a specialized probe that mechanically scans a conventional 2-D image transducer is used. However, since the mechanical scanning is slow, it is difficult to make 3D images of moving tissues. Recently, 2-D phased array transducers that can sweep the beam in 3-D have been developed. These can image faster and can even be used to make live 3-D images of a beating heart.
Doppler ultrasonography is used to study blood flow and muscle motion. The different detected speeds are represented in color for ease of interpretation, for example leaky heart valves: the leak shows up as a flash of unique color. Colors may alternatively be used to represent the amplitudes of the received echoes.
- A-mode: A-mode (amplitude mode) is the simplest. A single transducer scans a line through the body with the echoes plotted on screen as a function of depth. Therapeutic ultrasound aimed at a specific tumor or calculus is A-mode, to allow for pinpoint accurate focus of the destructive wave energy.
- B-mode or 2D mode: In B-mode (brightness mode), a linear array of transducers simultaneously scans a plane through the body that can be viewed as a two-dimensional image on screen. More commonly known as 2D mode now.
- B-flow is a mode that digitally highlights moving reflectors (mainly red blood cells) while suppressing the signals from the surrounding stationary tissue. It can visualize flowing blood and surrounding stationary tissues simultaneously. It is thus an alternative or complement to Doppler ultrasonography in visualizing blood flow.
- C-mode: A C-mode image is formed in a plane normal to a B-mode image. A gate that selects data from a specific depth from an A-mode line is used; then the transducer is moved in the 2D plane to sample the entire region at this fixed depth. When the transducer traverses the area in a spiral, an area of 100 cm2 can be scanned in around 10 seconds.
- M-mode: In M-mode (motion mode), pulses are emitted in quick succession – each time, either an A-mode or B-mode image is taken. Over time, this is analogous to recording a video in ultrasound. As the organ boundaries that produce reflections move relative to the probe, this can be used to determine the velocity of specific organ structures.
- Doppler mode: This mode makes use of the Doppler effect in measuring and visualizing blood flow
- Color Doppler: Velocity information is presented as a color-coded overlay on top of a B-mode image
- Continuous wave (CW) Doppler: Doppler information is sampled along a line through the body, and all velocities detected at each time point are presented (on a time line)
- Pulsed wave (PW) Doppler: Doppler information is sampled from only a small sample volume (defined in 2D image), and presented on a timeline
- Duplex: a common name for the simultaneous presentation of 2D and (usually) PW Doppler information. (Using modern ultrasound machines, color Doppler is almost always also used; hence the alternative name Triplex.)
- Pulse inversion mode: Two successive pulses with opposite sign are emitted and then subtracted from each other. This implies that any linearly responding constituent will disappear while gases with non-linear compressibility stand out. Pulse inversion may also be used in a similar manner as in Harmonic mode; see below:
- Harmonic mode: A deep penetrating fundamental frequency is emitted into the body and a harmonic overtone is detected. Noise and artifacts due to reverberation and aberration are greatly reduced. Some also believe that penetration depth can be gained with improved lateral resolution; however, this is not well documented.
An additional expansion of ultrasound is bi-planar ultrasound, in which the probe has two 2D planes perpendicular to each other, providing more efficient localization and detection. Furthermore, an omniplane probe can rotate 180° to obtain multiple images. In 3D ultrasound, many 2D planes are digitally added together to create a 3-dimensional image of the object.
Doppler ultrasonography employs the Doppler effect to assess whether structures (usually blood) are moving towards or away from the probe, and their relative velocity. By calculating the frequency shift of a particular sample volume, flow in an artery or a jet of blood flow over a heart valve, its speed and direction can be determined and visualized, as an example. Color Doppler is the measurement of velocity by color scale. Color Doppler images are generally combined with gray scale (B-mode) images to display duplex ultrasonography images. Uses include:
- Doppler echocardiography is the use of Doppler ultrasonography to examine the heart. An echocardiogram can, within certain limits, produce accurate assessment of the direction of blood flow and the velocity of blood and cardiac tissue at any arbitrary point using the Doppler effect. Velocity measurements allow assessment of cardiac valve areas and function, abnormal communications between the left and right side of the heart, leaking of blood through the valves (valvular regurgitation), and calculation of the cardiac output and E/A ratio (a measure of diastolic dysfunction). Contrast-enhanced ultrasound using gas-filled microbubble contrast media can be used to improve velocity or other flow-related measurements of interest.
- Transcranial Doppler (TCD) and transcranial color Doppler (TCCD), measure the velocity of blood flow through the brain's blood vessels through the cranium. They are useful in the diagnosis of emboli, stenosis, vasospasm from a subarachnoid hemorrhage (bleeding from a ruptured aneurysm), and other problems.
- Doppler fetal monitors use the Doppler effect to detect the fetal heartbeat during prenatal care. These are hand-held, and some models also display the heart rate in beats per minute (BPM). Use of this monitor is sometimes known as Doppler auscultation. The Doppler fetal monitor is commonly referred to simply as a Doppler or fetal Doppler and provides information similar to that provided by a fetal stethoscope.
Contrast ultrasonography (ultrasound contrast imaging)
A contrast medium for medical ultrasonography is a formulation of encapsulated gaseous microbubbles to increase echogenicity of blood, discovered by Dr Raymond Gramiak in 1968 and named contrast-enhanced ultrasound. This contrast medical imaging modality is used throughout the world, for echocardiography in particular in the United States and for ultrasound radiology in Europe and Asia.
Microbubbles-based contrast media is administrated intravenously into the patient blood stream during the ultrasonography examination. Due to their size, the microbubbles remain confined in blood vessels without extravasating towards the interstitial fluid. An ultrasound contrast media is therefore purely intravascular, making it an ideal agent to image organ microvascularization for diagnostic purposes. A typical clinical use of contrast ultrasonography is detection of a hypervascular metastatic tumor, which exhibits a contrast uptake (kinetics of microbubbles concentration in blood circulation) faster than healthy biological tissue surrounding the tumor. Other clinical applications using contrast exist, as in echocardiography to improve delineation of left ventricle for visualizing contractibility of heart muscle after a myocardial infarction. Finally, applications in quantitative perfusion (relative measurement of blood flow) have emerged for identifying early patient response to anti-cancerous drug treatment (methodology and clinical study by Dr Nathalie Lassau in 2011), enabling the best oncological therapeutic options to be determined.
In oncological practice of medical contrast ultrasonography, clinicians use 'parametric imaging of vascular signatures' invented by Dr Nicolas Rognin in 2010. This method is conceived as a cancer aided diagnostic tool, facilitating characterization of a suspicious tumor (malignant versus benign) in an organ. This method is based on medical computational science to analyze a time sequence of ultrasound contrast images, a digital video recorded in real-time during patient examination. Two consecutive signal processing steps are applied to each pixel of the tumor:
- calculation of a vascular signature (contrast uptake difference with respect to healthy tissue surrounding the tumor);
- automatic classification of the vascular signature into a unique parameter, the latter coded in one of the four following colors:
- green for continuous hyper-enhancement (contrast uptake higher than healthy tissue one),
- blue for continuous hypo-enhancement (contrast uptake lower than healthy tissue one),
- red for fast hyper-enhancement (contrast uptake before healthy tissue one) or
- yellow for fast hypo-enhancement (contrast uptake after healthy tissue one).
Once signal processing in each pixel is completed, a color spatial map of the parameter is displayed on a computer monitor, summarizing all vascular information of the tumor in a single image called a parametric image (see last figure of press article as clinical examples). This parametric image is interpreted by clinicians based on predominant colorization of the tumor: red indicates a suspicion of malignancy (risk of cancer), green or yellow – a high probability of benignity. In the first case (suspicion of malignant tumor), the clinician typically prescribes a biopsy to confirm the diagnostic or a CT scan examination as a second opinion. In the second case (quasi-certain of benign tumor), only a follow-up is needed with a contrast ultrasonography examination a few months later. The main clinical benefits are to avoid a systemic biopsy (with inherent risks of invasive procedures) of benign tumors or a CT scan examination exposing the patient to X-ray radiation. The parametric imaging of vascular signatures method proved to be effective in humans for characterization of tumors in the liver. In a cancer screening context, this method might be potentially applicable to other organs such as breast or prostate.
Molecular ultrasonography (ultrasound molecular imaging)
The current future of contrast ultrasonography is in molecular imaging with potential clinical applications expected in cancer screening to detect malignant tumors at their earliest stage of appearance. Molecular ultrasonography (or ultrasound molecular imaging) uses targeted microbubbles originally designed by Dr Alexander Klibanov in 1997; such targeted microbubbles specifically bind or adhere to tumoral microvessels by targeting biomolecular cancer expression (overexpression of certain biomolecules that occurs during neo-angiogenesis or inflammation in malignant tumors). As a result, a few minutes after their injection in blood circulation, the targeted microbubbles accumulate in the malignant tumor; facilitating its localization in a unique ultrasound contrast image. In 2013, the very first exploratory clinical trial in humans for prostate cancer was completed at Amsterdam in the Netherlands by Dr Hessel Wijkstra.
In molecular ultrasonography, the technique of acoustic radiation force (also used for shear wave elastography) is applied in order to literally push the targeted microbubbles towards microvessels wall; first demonstrated by Dr Paul Dayton in 1999. This allows maximization of binding to the malignant tumor; the targeted microbubbles being in more direct contact with cancerous biomolecules expressed at the inner surface of tumoral microvessels. At the stage of scientific preclinical research, the technique of acoustic radiation force was implemented as a prototype in clinical ultrasound systems and validated in vivo in 2D and 3D imaging modes.
Elastography (ultrasound elasticity imaging)
Ultrasound is also used for elastography, which is a relatively new imaging modality that maps the elastic properties of soft tissue. This modality emerged in the last two decades. Elastography is useful in medical diagnoses as it can discern healthy from unhealthy tissue for specific organs/growths. For example, cancerous tumors will often be harder than the surrounding tissue, and diseased livers are stiffer than healthy ones.
There are many ultrasound elastography techniques.
- Thyroid cysts: High frequency thyroid ultrasound (HFUS) can be used to treat several gland conditions. The recurrent thyroid cyst that was usually treated in the past with surgery, can be treated effectively by a new procedure called percutaneous ethanol injection, or PEI. With ultrasound guided placement of a 25 gauge needle within the cyst, and after evacuation of the cyst fluid, about 50% of the cyst volume is injected back into the cavity, under strict operator visualization of the needle tip. The procedure is 80% successful in reducing the cyst to minute size.
- Metastatic thyroid cancer neck lymph nodes: HFUS may also be used to treat metastatic thyroid cancer neck lymph nodes that occur in patients who either refuse, or are no longer candidates, for surgery. Small amounts of ethanol are injected under ultrasound guided needle placement. A power doppler blood flow study is done prior to injection. The blood flow can be destroyed and the node rendered inactive. Power doppler visualized blood flow can be eradicated, and there may be a drop in the cancer blood marker test, thyroglobulin, TG, as the node become non-functional. Another interventional use for HFUS is to mark a cancer node prior to surgery to help locate the node cluster at the surgery. A minute amount of methylene dye is injected, under careful ultrasound guided placement of the needle on the anterior surface, but not in the node. The dye will be evident to the thyroid surgeon when opening the neck. A similar localization procedure with methylene blue, can be done to locate parathyroid adenomas.
- Joint injections can be guided by medical ultrasound, such as in ultrasound-guided hip joint injections.
Compression ultrasonography is when the probe is pressed against the skin. This can bring the target structure closer to the probe, increasing spatial resolution of it. Comparison of the shape of the target structure before and after compression can aid in diagnosis.
It is used in ultrasonography of deep venous thrombosis, wherein absence of vein compressibility is a strong indicator of thrombosis. Compression ultrasonography has both high sensitivity and specificity for detecting proximal deep vein thrombosis in symptomatic patients. Results are not reliable when the patient is asymptomatic, for example in high risk postoperative orthopedic patients.
Panoramic ultrasonography is the digital stitching of multiple ultrasound images into a broader one. It can display an entire abnormality and show its relationship to nearby structures on a single image.
As with all imaging modalities, ultrasonography has positive and negative attributes.
- muscle, soft tissue, and bone surfaces are imaged very well including the delineation of interfaces between solid and fluid-filled spaces.
- "Live" images can be dynamically selected, permitting diagnosis and documentation often rapidly. Live images also permit ultrasound-guided biopsies or injections, which can be cumbersome with other imaging modalities.
- Organ structure can be demonstrated.
- There are no known long-term side effects when used according to guidelines, and discomfort is minimal.
- Ability to image local variations in the mechanical properties of soft tissue.
- Equipment is widely available and comparatively flexible.
- Small, easily carried scanners are available which permit bedside examinations.
- Transducers have become relatively inexpensive compared to other modes of investigation, such as computed X-ray tomography, DEXA or magnetic resonance imaging.
- Spatial resolution is better in high frequency ultrasound transducers than most other imaging modalities.
- Use of an ultrasound research interface can offer a relatively inexpensive, real-time, and flexible method for capturing data required for specific research purposes of tissue characterization and development of new image processing techniques.
- Sonographic devices have trouble penetrating bone. For example, sonography of the adult brain is currently very limited.
- Sonography performs very poorly when there is gas between the transducer and the organ of interest, due to the extreme differences in acoustic impedance. For example, overlying gas in the gastrointestinal tract often makes ultrasound scanning of the pancreas difficult. Lung imaging however can be useful in demarcating pleural effusions, detecting heart failure and pneumonia.
- Even in the absence of bone or air, the depth penetration of ultrasound may be limited depending on the frequency of imaging. Consequently, there might be difficulties imaging structures deep in the body, especially in obese patients.
- Image quality and accuracy of diagnosis is limited with obese patients and overlying subcutaneous fat attenuates the sound beam. A lower frequency transducer is required with subsequent lower resolution.
- The method is operator-dependent. Skill and experience is needed to acquire good-quality images and make accurate diagnoses.
- There is no scout image as there is with CT and MRI. Once an image has been acquired there is no exact way to tell which part of the body was imaged.
- 80% of sonographers suffer from Repetitive Strain Injuries (RSI) or so-called Work-Related Musculoskeletal Disorders (WMSD) because of bad ergonomic positions.
Risks and side-effects
- "Diagnostic ultrasound is recognized as a safe, effective, and highly flexible imaging modality capable of providing clinically relevant information about most parts of the body in a rapid and cost-effective fashion".
Diagnostic ultrasound studies of the fetus are generally considered to be safe during pregnancy. However, this diagnostic procedure should be performed only when there is a valid medical indication, and the lowest possible ultrasonic exposure setting should be used to gain the necessary diagnostic information under the "as low as reasonably practicable" or ALARP principle.
Although there is no evidence that ultrasound could be harmful to the fetus, medical authorities typically strongly discourage the promotion, selling, or leasing of ultrasound equipment for making "keepsake fetal videos".
Studies on the safety of ultrasound
- A meta-analysis of several ultrasonography studies published in 2000 found no statistically significant harmful effects from ultrasonography. It was noted that there is a lack of data on long-term substantive outcomes such as neurodevelopment.
- A study at the Yale School of Medicine published in 2006 found a small but significant correlation between prolonged and frequent use of ultrasound and abnormal neuronal migration in mice.
- A study performed in Sweden in 2001 has shown that subtle effects of neurological damage linked to ultrasound were implicated by an increased incidence in left-handedness in boys (a marker for brain problems when not hereditary) and speech delays.
Diagnostic and therapeutic ultrasound equipment is regulated in the US by the Food and Drug Administration, and worldwide by other national regulatory agencies. The FDA limits acoustic output using several metrics; generally, other agencies accept the FDA-established guidelines.
Currently, New Mexico, Oregon, and North Dakota are the only US states that regulate diagnostic medical sonographers. Certification examinations for sonographers are available in the US from three organizations: the American Registry for Diagnostic Medical Sonography, Cardiovascular Credentialing International and the American Registry of Radiologic Technologists.
The primary regulated metrics are Mechanical Index (MI), a metric associated with the cavitation bio-effect, and Thermal Index (TI) a metric associated with the tissue heating bio-effect. The FDA requires that the machine not exceed established limits, which are reasonably conservative in an effort to maintain diagnostic ultrasound as a safe imaging modality. This requires self-regulation on the part of the manufacturer in terms of machine calibration.
Ultrasound-based pre-natal care and sex screening technologies were launched in India in the 1980s. With concerns about its misuse for sex-selective abortion, the Government of India passed the Pre-natal Diagnostic Techniques Act (PNDT) in 1994 to distinguish and regulate legal and illegal uses of ultrasound equipment. The law was further amended as the Pre-Conception and Pre-natal Diagnostic Techniques (Regulation and Prevention of Misuse) (PCPNDT) Act in 2004 to deter and punish prenatal sex screening and sex selective abortion. It is currently illegal and a punishable crime in India to determine or disclose the sex of a fetus using ultrasound equipment.
After the French physicist Pierre Curie’s discovery of piezoelectricity in 1880, ultrasonic waves could be deliberately generated for industry. In 1940, the American acoustical physicist Floyd Firestone devised the first ultrasonic echo imaging device, the Supersonic Reflectoscope, to detect internal flaws in metal castings. In 1941, Austrian neurologist Karl Theo Dussik, in collaboration with his brother, Friedrich, a physicist, was likely the first person to image the human body ultrasonically, outlining the ventricles of a human brain. Ultrasonic energy was first applied to the human body for medical purposes by Dr George Ludwig at the Naval Medical Research Institute, Bethesda, Maryland, in the late 1940s. English-born physicist John Wild (1914–2009) first used ultrasound to assess the thickness of bowel tissue as early as 1949; he has been described as the "father of medical ultrasound". Subsequent advances took place concurrently in several countries but was not until 1961 when David Robinson and George Kossoff's work at the Australian Department of Health resulted in the first commercially practical water bath ultrasonic scanner. In 1963 Meyerdirk & Wright launched production of the first commercial, hand-held, articulated arm, compound contact B-mode scanner, which made ultrasound generally available for medical use.
Léandre Pourcelot, a researcher and teacher at INSA (Institut National des Sciences Appliquées), Lyon, co-published a report in 1965 at the Académie des sciences, "Effet Doppler et mesure du débit sanguin" ("Doppler effect and measure of the blood flow"), the basis of his design of a Doppler flow meter in 1967.
Parallel developments in Glasgow, Scotland by Professor Ian Donald and colleagues at the Glasgow Royal Maternity Hospital (GRMH) led to the first diagnostic applications of the technique. Donald was an obstetrician with a self-confessed "childish interest in machines, electronic and otherwise", who, having treated the wife of one of the company's directors, was invited to visit the Research Department of boilermakers Babcock & Wilcox at Renfrew. He adapted their industrial ultrasound equipment to conduct experiments on various morbid anatomical specimens and assess their ultrasonic characteristics. Together with the medical physicist Tom Brown. and fellow obstetrician Dr John MacVicar, Donald refined the equipment to enable differentiation of pathology in live volunteer patients. These findings were reported in The Lancet on 7 June 1958 as "Investigation of Abdominal Masses by Pulsed Ultrasound" – possibly one of the most important papers published in the field of diagnostic medical imaging.
At GRMH, Professor Donald and Dr James Willocks then refined their techniques to obstetric applications including fetal head measurement to assess the size and growth of the fetus. With the opening of the new Queen Mother's Hospital in Yorkhill in 1964, it became possible to improve these methods even further. Dr Stuart Campbell's pioneering work on fetal cephalometry led to it acquiring long-term status as the definitive method of study of foetal growth. As the technical quality of the scans was further developed, it soon became possible to study pregnancy from start to finish and diagnose its many complications such as multiple pregnancy, fetal abnormality and placenta praevia. Diagnostic ultrasound has since been imported into practically every other area of medicine.
Medical ultrasonography was used in 1953 at Lund University by cardiologist Inge Edler and Gustav Ludwig Hertz's son Carl Hellmuth Hertz, who was then a graduate student at the university's department of nuclear physics.
Edler had asked Hertz if it was possible to use radar to look into the body, but Hertz said this was impossible. However, he said, it might be possible to use ultrasonography. Hertz was familiar with using ultrasonic reflectoscopes of the American acoustical physicist Floyd Firestone's invention for nondestructive materials testing, and together Edler and Hertz developed the idea of applying this methodology in medicine.
The first successful measurement of heart activity was made on October 29, 1953, using a device borrowed from the ship construction company Kockums in Malmö. On December 16 the same year, the method was applied to generate an echo-encephalogram (ultrasonic probe of the brain). Edler and Hertz published their findings in 1954.
In 1962, after about two years of work, Joseph Holmes, William Wright, and Ralph Meyerdirk developed the first compound contact B-mode scanner. Their work had been supported by U.S. Public Health Services and the University of Colorado. Wright and Meyerdirk left the university to form Physionic Engineering Inc., which launched the first commercial hand-held articulated arm compound contact B-mode scanner in 1963. This was the start of the most popular design in the history of ultrasound scanners.
In the late 1960s Dr Gene Strandness and the bio-engineering group at the University of Washington conducted research on Doppler ultrasound as a diagnostic tool for vascular disease. Eventually, they developed technologies to use duplex imaging, or Doppler in conjunction with B-mode scanning, to view vascular structures in real time while also providing hemodynamic information.
The first demonstration of color Doppler was by Geoff Stevenson, who was involved in the early developments and medical use of Doppler shifted ultrasonic energy.
The leading manufacturers of ultrasound equipment are Canon Medical, FUJIFILM SonoSite, GE Healthcare, Hitachi, Philips and Siemens Healthineers. Companies such as Usono design, develop, and sell accessories to make the use of ultrasound easier.
- It is for this reason that the person subjected to ultrasound of organs that can contain quantities of air or gas, such as the stomach, intestine and bladder, must follow a food preparation designed to reduce their quantity: specific diet and supplements for the intestine and intake of non-carbonated water to fill the bladder; sometimes, during the examination, it may be required to fill the stomach with non-carbonated water.
- Aldrich JE. Basic physics of ultrasound imaging. Crit Care Med. 2007 May;35(5 Suppl):S131-7. doi: 10.1097/01.CCM.0000260624.99430.22. PMID 17446771
- Izadifar Z, Babyn P, Chapman D. Mechanical and Biological Effects of Ultrasound: A Review of Present Knowledge. Ultrasound Med Biol. 2017 Jun;43(6):1085-1104. doi: 10.1016/j.ultrasmedbio.2017.01.023. Epub 2017 Mar 23. PMID 28342566
- Amaral CB, Ralston DC, Becker TK. Prehospital point-of-care ultrasound: A transformative technology. SAGE Open Med. 2020 Jul 26;8:2050312120932706. doi: 10.1177/2050312120932706. PMID 32782792; PMCID: PMC7383635.
- Garcìa-Garcìa HM, Gogas BD, Serruys PW, Bruining N (February 2011). "IVUS-based imaging modalities for tissue characterization: similarities and differences". Int J Cardiovasc Imaging. 27 (2): 215–24. doi:10.1007/s10554-010-9789-7. PMC 3078312. PMID 21327914.
- Ultrasound Guidelines: Emergency, Point-of-Care and Clinical Ultrasound Guidelines in Medicine. Ann Emerg Med. 2017 May;69(5):e27-e54. doi: 10.1016/j.annemergmed.2016.08.457. PMID 28442101
- Harvey CJ, Albrecht T. Ultrasound of focal liver lesions. Eur Radiol. 2001;11(9):1578-93. doi: 10.1007/s003300101002. PMID 11511877.
- Dubose, T. J. (1985). "Fetal Biometry: Vertical Calvarial Diameter and Calvarial Volume". Journal of Diagnostic Medical Sonography. 1 (5): 205–217. doi:10.1177/875647938500100504. S2CID 73129628.
- Dubose, Terry (July 14, 2011). "3D BPD Correction". Archived from the original on March 3, 2016. Retrieved 2015-01-14.
- Hellman LM, Duffus GM, Donald I, Sundén B. Safety of diagnostic ultrasound in obstetrics. Lancet. 1970 May 30;1(7657):1133-4. doi: 10.1016/s0140-6736(70)91212-2. PMID 4192094.
- Campbell S. A short history of sonography in obstetrics and gynaecology. Facts Views Vis Obgyn. 2013;5(3):213-29. PMID 24753947; PMCID: PMC3987368.
- "Avoid Fetal "Keepsake" Images, Heartbeat Monitors". U.S. food and Drug Administration. U.S. Government. Archived from the original on April 23, 2019. Retrieved 11 September 2017.
- Clinical Safety Statements Archived 2012-06-26 at the Wayback Machine. Efsumb.org. Retrieved on 2011-11-13.
- "Applications » Uscom".
- Ghervan C. Thyroid and parathyroid ultrasound. Med Ultrason. 2011 Mar;13(1):80-4. PMID 21390348.
- Yoshida H, Yasuhara A, Kobayashi Y. Transcranial Doppler sonographic studies of cerebral blood flow velocity in neonates. Pediatr Neurol. 1991 Mar-Apr;7(2):105-10. doi: 10.1016/0887-8994(91)90005-6. PMID 2059249.
- Gottlieb M, Holladay D, Peksa GD. Point-of-Care Ocular Ultrasound for the Diagnosis of Retinal Detachment: A Systematic Review and Meta-Analysis. Acad Emerg Med. 2019 Aug;26(8):931-939. doi: 10.1111/acem.13682. Epub 2019 Feb 5. PMID 30636351
- Kilker BA, Holst JM, Hoffmann B. Bedside ocular ultrasound in the emergency department. Eur J Emerg Med. 2014 Aug;21(4):246-53. doi: 10.1097/MEJ.0000000000000070. PMID 24002686
- "UpToDate". www.uptodate.com. Retrieved 2019-07-23.
- "Lung Ultrasound Simulator". Retrieved 2021-09-30.
- Lichtenstein, Daniel (2016). Lung Ultrasound in the Critically Ill: The BLUE Protocol. Springer. ISBN 978-3-319-15370-4.
- Husain, LubnaF; Wayman, Derek; Carmody, KristinA; Hagopian, Laura; Baker, WilliamE (2012). "Sonographic diagnosis of pneumothorax". Journal of Emergencies, Trauma, and Shock. 5 (1): 76–81. doi:10.4103/0974-2700.93116. ISSN 0974-2700. PMC 3299161. PMID 22416161.
- Blanco, Pablo A.; Cianciulli, Tomás F. (2016). "Pulmonary Edema Assessed by Ultrasound: Impact in Cardiology and Intensive Care Practice". Echocardiography. 33 (5): 778–787. doi:10.1111/echo.13182. PMID 26841270. S2CID 37476194.
- Soldati, Gino; Demi, Marcello (2017). "The use of lung ultrasound images for the differential diagnosis of pulmonary and cardiac interstitial pathology". Journal of Ultrasound. 20 (2): 91–96. doi:10.1007/s40477-017-0244-7. ISSN 1876-7931. PMC 5440336. PMID 28592998.
- International Liaison Committee on Lung Ultrasound (ILC-LUS) for the International Consensus Conference on Lung Ultrasound (ICC-LUS); Volpicelli, Giovanni; Elbarbary, Mahmoud; Blaivas, Michael; Lichtenstein, Daniel A.; Mathis, Gebhard; Kirkpatrick, Andrew W.; Melniker, Lawrence; Gargani, Luna (2012). "International evidence-based recommendations for point-of-care lung ultrasound". Intensive Care Medicine. 38 (4): 577–591. doi:10.1007/s00134-012-2513-4. ISSN 0342-4642. PMID 22392031.
- Brogi, E.; Gargani, L.; Bignami, E.; Barbariol, F.; Marra, A.; Forfori, F.; Vetrugno, L. (2017). "Thoracic ultrasound for pleural effusion in the intensive care unit: a narrative review from diagnosis to treatment". Critical Care. 21 (1): 325. doi:10.1186/s13054-017-1897-5. ISSN 1364-8535. PMC 5745967. PMID 29282107.
- Herth, F J F; Eberhardt, R; Vilmann, P; Krasnik, M; Ernst, A (2006). "Real-time endobronchial ultrasound guided transbronchial needle aspiration for sampling mediastinal lymph nodes". Thorax. 61 (9): 795–8. doi:10.1136/thx.2005.047829. PMC 2117082. PMID 16738038.
- Lesser, FD; Smallwood, N; Dachsel, M (1 August 2021). "Point-of-care lung ultrasound during and after the COVID-19 pandemic". Ultrasound. 29 (3): 140. doi:10.1177/1742271X211033737. S2CID 236980540.
- Knight, T.; Parulekar, P.; Rudge, G.; Lesser, F.; Dachsel, M.; Aujayeb, A.; Lasserson, D.; Smallwood, N. (1 November 2021). "S68 National COVID point of care lung ultrasound evaluation (society for acute medicine with the intensive care society)". Thorax. 76 (Suppl 2): A44–A45. doi:10.1136/thorax-2021-BTSabstracts.74.
- Piloni, Vittorio Luigi; Spazzafumo, Liana (June 2007). "Sonography of the female pelvic floor:clinical indications and techniques". Pelviperineology. 26 (2): 59–65.
- Graham, Sam D.; Thomas E Keane (25 September 2009). Glenn's Urologic Surgery. Lippincott Williams & Wilkins. pp. 433–. ISBN 978-0-7817-9141-0. Retrieved 1 July 2011.
- Originally copied from:
Fernandes, Maitê Aline Vieira; Souza, Luis Ronan Marquez Ferreira de; Cartafina, Luciano Pousa (2018). "Ultrasound evaluation of the penis". Radiologia Brasileira. 51 (4): 257–261. doi:10.1590/0100-3984.2016.0152. ISSN 1678-7099. PMC 6124582. PMID 30202130.
- Arend CF. Ultrasound of the Shoulder. Porto Alegre: Master Medical Books; 2013. (Free access at ShoulderUS.com)[page needed]
- Hübner U, Schlicht W, Outzen S, Barthel M, Halsband H. Ultrasound in the diagnosis of fractures in children. J Bone Joint Surg Br. 2000 Nov;82(8):1170-3. doi: 10.1302/0301-620x.82b8.10087. PMID 11132281.
- Zaidman, Craig M.; van Alfen, Nens (2016-04-01). "Ultrasound in the Assessment of Myopathic Disorders". Journal of Clinical Neurophysiology. 33 (2): 103–111. doi:10.1097/WNP.0000000000000245. PMID 27035250. S2CID 35805733.
- Harris-Love, Michael O.; Monfaredi, Reza; Ismail, Catheeja; Blackman, Marc R.; Cleary, Kevin (2014-01-01). "Quantitative ultrasound: measurement considerations for the assessment of muscular dystrophy and sarcopenia". Frontiers in Aging Neuroscience. 6: 172. doi:10.3389/fnagi.2014.00172. PMC 4094839. PMID 25071570.
- Abe, Takashi; Loene, Jeremy P.; Young, Kaelin C.; Thiebaud, Robert S.; Nahar, Vinayak K.; Hollaway, Kaitlyn M.; Stover, Caitlin D.; Ford, M. Allison; Bass, Martha A. (2015-02-01). "Validity of ultrasound prediction equations for total and regional muscularity in middle-aged and older men and women". Ultrasound in Medicine & Biology. 41 (2): 557–564. doi:10.1016/j.ultrasmedbio.2014.09.007. PMID 25444689.
- McGregor, Robin A.; Cameron-Smith, David; Poppitt, Sally D. (2014-01-01). "It is not just muscle mass: a review of muscle quality, composition and metabolism during ageing as determinants of muscle function and mobility in later life". Longevity & Healthspan. 3 (1): 9. doi:10.1186/2046-2395-3-9. PMC 4268803. PMID 25520782.
- Watanabe, Yuya; Yamada, Yosuke; Fukumoto, Yoshihiro; Ishihara, Tatsuro; Yokoyama, Keiichi; Yoshida, Tsukasa; Miyake, Motoko; Yamagata, Emi; Kimura, Misaka (2013-01-01). "Echo intensity obtained from ultrasonography images reflecting muscle strength in elderly men". Clinical Interventions in Aging. 8: 993–998. doi:10.2147/CIA.S47263. PMC 3732157. PMID 23926426.
- Ismail, Catheeja; Zabal, Johannah; Hernandez, Haniel J.; Woletz, Paula; Manning, Heather; Teixeira, Carla; DiPietro, Loretta; Blackman, Marc R.; Harris-Love, Michael O. (2015-01-01). "Diagnostic ultrasound estimates of muscle mass and muscle quality discriminate between women with and without sarcopenia". Frontiers in Physiology. 6: 302. doi:10.3389/fphys.2015.00302. PMC 4625057. PMID 26578974.
- Content initially copied from: Hansen, Kristoffer; Nielsen, Michael; Ewertsen, Caroline (2015). "Ultrasonography of the Kidney: A Pictorial Review". Diagnostics. 6 (1): 2. doi:10.3390/diagnostics6010002. ISSN 2075-4418. PMC 4808817. PMID 26838799. (CC-BY 4.0)
- Pavlin, Charles; Foster, F. Stuart (1994). Ultrasound Biomicroscopy of the Eye. Springer. ISBN 978-0-387-94206-3.
- Ng, Alexander; Swanevelder, Justiaan (October 2011). "Resolution in ultrasound imaging". Continuing Education in Anaesthesia, Critical Care & Pain. 11 (5): 186–192. doi:10.1093/bjaceaccp/mkr030.
- Ostensen, Harald (2005). Basic physics of ultrasound imaging (PDF). Geneva: Diagnostic Imaging and Laboratory Technology - World Health Organisation. pp. 25–26. Retrieved 2 October 2021.
- The Gale Encyclopedia of Medicine, 2nd Edition, Vol. 1 A-B. p. 4
- Cobbold, Richard S. C. (2007). Foundations of Biomedical Ultrasound. Oxford University Press. pp. 422–423. ISBN 978-0-19-516831-0.
- Tzou DT, Usawachintachit M, Taguchi K, Chi T. Ultrasound Use in Urinary Stones: Adapting Old Technology for a Modern-Day Disease. J Endourol. 2017 Apr;31(S1):S89-S94. doi: 10.1089/end.2016.0584. Epub 2016 Nov 3. PMID 27733052; PMCID: PMC5397246.
- Wang, Hsin-Kai; Chou, Yi-Hong; Chiou, Hong-Jen; Chiou, See-Ying; Chang, Cheng-Yen (2005). "B-flow Ultrasonography of Peripheral Vascular Diseases". Journal of Medical Ultrasound. 13 (4): 186–195. doi:10.1016/S0929-6441(09)60108-9. ISSN 0929-6441.
- Wachsberg, Ronald H. (2007). "B-Flow Imaging of the Hepatic Vasculature: Correlation with Color Doppler Sonography". American Journal of Roentgenology. 188 (6): W522–W533. doi:10.2214/AJR.06.1161. ISSN 0361-803X. PMID 17515342.
- Page 161 (part II > Two-dimensional Echocardiography) in: Reves, J. G.; Estafanous, Fawzy G.; Barash, Paul G. (2001). Cardiac anesthesia: principles and clinical practice. Hagerstwon, MD: Lippincott Williams & Wilkins. ISBN 978-0-7817-2195-0.
- Franceschi, Claude (1978). L'Investigation vasculaire par ultrasonographie doppler. Masson. ISBN 978-2-225-63679-0.
- Saxena, A; Ng, EYK; Lim, ST (28 May 2019). "Imaging modalities to diagnose carotid artery stenosis: progress and prospect". BioMedical Engineering OnLine. 18 (1): 66. doi:10.1186/s12938-019-0685-7. PMC 6537161. PMID 31138235.
- "Echocardiogram". MedlinePlus. Retrieved 2017-12-15.
-  Abdul Latif Mohamed, Jun Yong, Jamil Masiyati, Lee Lim, Sze Chec Tee. The Prevalence Of Diastolic Dysfunction In Patients With Hypertension Referred For Echocardiographic Assessment of Left Ventricular Function. Malaysian Journal of Medical Sciences, Vol. 11, No. 1, January 2004, pp. 66-74
- Schneider, Michel (1999). "Characteristics of SonoVue™". Echocardiography. 16 (7, Pt 2): 743–746. doi:10.1111/j.1540-8175.1999.tb00144.x. PMID 11175217. S2CID 73314302.
- Gramiak, Raymond; Shah, Pravin M. (1968). "Echocardiography of the Aortic Root". Investigative Radiology. 3 (5): 356–66. doi:10.1097/00004424-196809000-00011. PMID 5688346.
- "CEUS Around the World – The International Contrast Ultrasound Society (ICUS)" (PDF). October 2013. Archived from the original (PDF) on October 29, 2013. Retrieved 2013-10-27.
- Claudon, Michel; Dietrich, Christoph F.; Choi, Byung Ihn; Cosgrove, David O.; Kudo, Masatoshi; Nolsøe, Christian P.; Piscaglia, Fabio; Wilson, Stephanie R.; Barr, Richard G.; Chammas, Maria C.; Chaubal, Nitin G.; Chen, Min-Hua; Clevert, Dirk Andre; Correas, Jean Michel; Ding, Hong; Forsberg, Flemming; Fowlkes, J. Brian; Gibson, Robert N.; Goldberg, Barry B.; Lassau, Nathalie; Leen, Edward L.S.; Mattrey, Robert F.; Moriyasu, Fuminori; Solbiati, Luigi; Weskott, Hans-Peter; Xu, Hui-Xiong; World Federation for Ultrasound in Medicine; European Federation of Societies for Ultrasound (2013). "Guidelines and Good Clinical Practice Recommendations for Contrast Enhanced Ultrasound (CEUS) in the Liver – Update 2012". Ultrasound in Medicine & Biology. 39 (2): 187–210. doi:10.1016/j.ultrasmedbio.2012.09.002. PMID 23137926.
- Piscaglia, F.; Nolsøe, C.; Dietrich, C.; Cosgrove, D.; Gilja, O.; Bachmann Nielsen, M.; Albrecht, T.; Barozzi, L.; Bertolotto, M.; Catalano, O.; Claudon, M.; Clevert, D.; Correas, J.; d'Onofrio, M.; Drudi, F.; Eyding, J.; Giovannini, M.; Hocke, M.; Ignee, A.; Jung, E.; Klauser, A.; Lassau, N.; Leen, E.; Mathis, G.; Saftoiu, A.; Seidel, G.; Sidhu, P.; Ter Haar, G.; Timmerman, D.; Weskott, H. (2011). "The EFSUMB Guidelines and Recommendations on the Clinical Practice of Contrast Enhanced Ultrasound (CEUS): Update 2011 on non-hepatic applications". Ultraschall in der Medizin. 33 (1): 33–59. doi:10.1055/s-0031-1281676. PMID 21874631.
- Tang, M.- X.; Mulvana, H.; Gauthier, T.; Lim, A. K. P.; Cosgrove, D. O.; Eckersley, R. J.; Stride, E. (2011). "Quantitative contrast-enhanced ultrasound imaging: A review of sources of variability". Interface Focus. 1 (4): 520–39. doi:10.1098/rsfs.2011.0026. PMC 3262271. PMID 22866229.
- Lassau, N.; Koscielny, S.; Chami, L.; Chebil, M.; Benatsou, B.; Roche, A.; Ducreux, M.; Malka, D.; Boige, V. (2010). "Advanced Hepatocellular Carcinoma: Early Evaluation of Response to Bevacizumab Therapy at Dynamic Contrast-enhanced US with Quantification—Preliminary Results". Radiology. 258 (1): 291–300. doi:10.1148/radiol.10091870. PMID 20980447.
- Sugimoto, Katsutoshi; Moriyasu, Fuminori; Saito, Kazuhiro; Rognin, Nicolas; Kamiyama, Naohisa; Furuichi, Yoshihiro; Imai, Yasuharu (2013). "Hepatocellular carcinoma treated with sorafenib: Early detection of treatment response and major adverse events by contrast-enhanced US". Liver International. 33 (4): 605–15. doi:10.1111/liv.12098. PMID 23305331. S2CID 19338115.
- Rognin, N G; Arditi, M; Mercier, L; Frinking, P J A; Schneider, M; Perrenoud, G; Anaye, A; Meuwly, J; Tranquart, F (2010). "Parametric imaging for characterizing focal liver lesions in contrast-enhanced ultrasound". IEEE Transactions on Ultrasonics, Ferroelectrics and Frequency Control. 57 (11): 2503–11. doi:10.1109/TUFFC.2010.1716. PMID 21041137. S2CID 19339331.
- Rognin N, et al. (2010). "Parametric images based on dynamic behavior over time". International Patent. World Intellectual Property Organization (WIPO). pp. 1–44.
- Tranquart, F.; Mercier, L.; Frinking, P.; Gaud, E.; Arditi, M. (2012). "Perfusion Quantification in Contrast-Enhanced Ultrasound (CEUS) – Ready for Research Projects and Routine Clinical Use". Ultraschall in der Medizin. 33: S31–8. doi:10.1055/s-0032-1312894. PMID 22723027.
- Angelelli, Paolo; Nylund, Kim; Gilja, Odd Helge; Hauser, Helwig (2011). "Interactive visual analysis of contrast-enhanced ultrasound data based on small neighborhood statistics". Computers & Graphics. 35 (2): 218–226. doi:10.1016/j.cag.2010.12.005.
- Barnes E, Contrast US processing tool shows malignant liver lesions, AuntMinnie.com, 2010.
- Anaye, A.; Perrenoud, G.; Rognin, N.; Arditi, M.; Mercier, L.; Frinking, P.; Ruffieux, C.; Peetrons, P.; Meuli, R.; Meuwly, J.-Y. (2011). "Differentiation of Focal Liver Lesions: Usefulness of Parametric Imaging with Contrast-enhanced US". Radiology. 261 (1): 300–10. doi:10.1148/radiol.11101866. PMID 21746815.
- Yuan, Zhang; Quan, Jiang; Yunxiao, Zhang; Jian, Chen; Zhu, He; Liping, Gong (2013). "Diagnostic Value of Contrast-Enhanced Ultrasound Parametric Imaging in Breast Tumors". Journal of Breast Cancer. 16 (2): 208–13. doi:10.4048/jbc.2013.16.2.208. PMC 3706868. PMID 23843855.
- Klibanov, A. L.; Hughes, M. S.; Marsh, J. N.; Hall, C. S.; Miller, J. G.; Wilble, J. H.; Brandenburger, G. H. (1997). "Targeting of ultrasound contrast material. An in vitro feasibility study". Acta Radiologica Supplementum. 412: 113–120. PMID 9240089.
- Klibanov, A (1999). "Targeted delivery of gas-filled microspheres, contrast agents for ultrasound imaging". Advanced Drug Delivery Reviews. 37 (1–3): 139–157. doi:10.1016/S0169-409X(98)00104-5. PMID 10837732.
- Pochon, S; Tardy, I; Bussat, P; Bettinger, T; Brochot, J; Von Wronski, M; Passantino, L; Schneider, M (2010). "BR55: A lipopeptide-based VEGFR2-targeted ultrasound contrast agent for molecular imaging of angiogenesis". Investigative Radiology. 45 (2): 89–95. doi:10.1097/RLI.0b013e3181c5927c. PMID 20027118. S2CID 24089981.
- Willmann, J. K.; Kimura, R. H.; Deshpande, N.; Lutz, A. M.; Cochran, J. R.; Gambhir, S. S. (2010). "Targeted Contrast-Enhanced Ultrasound Imaging of Tumor Angiogenesis with Contrast Microbubbles Conjugated to Integrin-Binding Knottin Peptides". Journal of Nuclear Medicine. 51 (3): 433–40. doi:10.2967/jnumed.109.068007. PMC 4111897. PMID 20150258.
- Lindner, JR (2004). "Molecular imaging with contrast ultrasound and targeted microbubbles". Journal of Nuclear Cardiology. 11 (2): 215–21. doi:10.1016/j.nuclcard.2004.01.003. PMID 15052252. S2CID 36487102.
- Clinical trial number NCT01253213 for "BR55 in Prostate Cancer: an Exploratory Clinical Trial" at ClinicalTrials.gov
- Dayton, Paul; Klibanov, Alexander; Brandenburger, Gary; Ferrara, Kathy (1999). "Acoustic radiation force in vivo: A mechanism to assist targeting of microbubbles". Ultrasound in Medicine & Biology. 25 (8): 1195–1201. doi:10.1016/S0301-5629(99)00062-9. PMID 10576262.
- Frinking, Peter J.A.; Tardy, Isabelle; Théraulaz, Martine; Arditi, Marcel; Powers, Jeffry; Pochon, Sibylle; Tranquart, François (2012). "Effects of Acoustic Radiation Force on the Binding Efficiency of BR55, a VEGFR2-Specific Ultrasound Contrast Agent". Ultrasound in Medicine & Biology. 38 (8): 1460–9. doi:10.1016/j.ultrasmedbio.2012.03.018. PMID 22579540.
- Gessner, Ryan C.; Streeter, Jason E.; Kothadia, Roshni; Feingold, Steven; Dayton, Paul A. (2012). "An In Vivo Validation of the Application of Acoustic Radiation Force to Enhance the Diagnostic Utility of Molecular Imaging Using 3-D Ultrasound". Ultrasound in Medicine & Biology. 38 (4): 651–60. doi:10.1016/j.ultrasmedbio.2011.12.005. PMC 3355521. PMID 22341052.
- Rognin N; et al. (2013). "Molecular Ultrasound Imaging Enhancement by Volumic Acoustic Radiation Force (VARF): Pre-clinical in vivo Validation in a Murine Tumor Model". World Molecular Imaging Congress, Savannah, GA, USA. Archived from the original on October 11, 2013.
- Wells P. N. T. (2011). "Medical ultrasound: imaging of soft tissue strain and elasticity". Journal of the Royal Society, Interface. 8 (64): 1521–1549. doi:10.1098/rsif.2011.0054. PMC 3177611. PMID 21680780.
- Sarvazyan A, Hall TJ, Urban MW, Fatemi M, Aglyamov SR, Garra BS (2011). "Overview of elastography–an emerging branch of medical imaging". Current Medical Imaging Reviews. 7 (4): 255–282. doi:10.2174/157340511798038684. PMC 3269947. PMID 22308105.
- Ophir, J.; Céspides, I.; Ponnekanti, H.; Li, X. (1991). "Elastography: A quantitative method for imaging the elasticity of biological tissues". Ultrasonic Imaging. 13 (2): 111–34. doi:10.1016/0161-7346(91)90079-W. PMID 1858217.
- Parker, K J; Doyley, M M; Rubens, D J (2012). "Corrigendum: Imaging the elastic properties of tissue: The 20 year perspective". Physics in Medicine and Biology. 57 (16): 5359–5360. Bibcode:2012PMB....57.5359P. doi:10.1088/0031-9155/57/16/5359.
- Halenka M, Karasek D, Schovanek J, Frysak Z. Safe and effective percutaneous ethanol injection therapy of 200 thyroid cysts. Biomed Pap Med Fac Univ Palacky Olomouc Czech Repub. 2020 Jun;164(2):161-167. doi: 10.5507/bp.2019.007. Epub 2019 Mar 29. PMID 30945701.
- Temizkan S. PERCUTANEOUS ETHANOL INJECTION FOR BENIGN CYSTIC AND MIXED THYROID NODULES. Endocr Pract. 2018 Jun;24(6):548-555. doi: 10.4158/EP-2018-0013. Epub 2018 Apr 6. PMID 29624094.
- Yeap, Phey Ming; Robinson, Philip (2017). "Ultrasound Diagnostic and Therapeutic Injections of the Hip and Groin". Journal of the Belgian Society of Radiology. 101 (S2): 6. doi:10.5334/jbr-btr.1371. ISSN 2514-8281. PMC 6251072. PMID 30498802.
Creative Commons Attribution 4.0 International License (CC-BY 4.0)
- Cogo, A.; Lensing, A. W A; Koopman, M. M W; Piovella, F.; Siragusa, S.; Wells, P. S; Villalta, S.; Büller, H. R; Turpie, A. G G; Prandoni, P. (1998). "Compression ultrasonography for diagnostic management of patients with clinically suspected deep vein thrombosis: Prospective cohort study". BMJ. 316 (7124): 17–20. doi:10.1136/bmj.316.7124.17. PMC 2665362. PMID 9451260.
- Kearon, Clive; Julian, JA; Newman, TE; Ginsberg, JS (1998). "Noninvasive Diagnosis of Deep Venous Thrombosis". Annals of Internal Medicine. 128 (8): 663–77. doi:10.7326/0003-4819-128-8-199804150-00011. PMID 9537941. S2CID 13467218.
- Jongbloets, L.M.M.; Koopman, M.M.W.; Büller, H.R.; Ten Cate, J.W.; Lensing, A.W.A. (1994). "Limitations of compression ultrasound for the detection of symptomless postoperative deep vein thrombosis". The Lancet. 343 (8906): 1142–4. doi:10.1016/S0140-6736(94)90240-2. PMID 7910237. S2CID 23576444.
- Reddan, Tristan; Corness, Jonathan; Mengersen, Kerrie; Harden, Fiona (March 2016). "Ultrasound of paediatric appendicitis and its secondary sonographic signs: providing a more meaningful finding". Journal of Medical Radiation Sciences. 63 (1): 59–66. doi:10.1002/jmrs.154. PMC 4775827. PMID 27087976.
- Kumar, Suresh. "Panoramic Ultrasound". Conference: Proceedings of the Second National Conference on Signal & Image Processing, at S.M.K. Fomra Institute of Technology Chennai, India. April 2010
- Nightingale KR, Soo MS, Nightingale R, Trahey GE (2002). "Acoustic radiation force impulse imaging: in vivo demonstration of clinical feasibility". Ultrasound in Medicine & Biology. 28 (2): 227–235. doi:10.1016/s0301-5629(01)00499-9. PMID 11937286.CS1 maint: multiple names: authors list (link)
- Llamas-Álvarez, AM; Tenza-Lozano, EM; Latour-Pérez, J (February 2017). "Accuracy of Lung Ultrasonography in the Diagnosis of Pneumonia in Adults: Systematic Review and Meta-Analysis". Chest. 151 (2): 374–382. doi:10.1016/j.chest.2016.10.039. PMID 27818332. S2CID 24399240.
- Merritt, CR (1989). "Ultrasound safety: What are the issues?". Radiology. 173 (2): 304–6. doi:10.1148/radiology.173.2.2678243. PMID 2678243.[dead link]
- "Training in Diagnostic Ultrasound: essentials, principles and standards" (PDF). WHO. 1998. p. 2.
- "Official Statement". www.aium.org. Retrieved 2020-05-19.
- Lockwook, Charles J. (November 2010). "Keepsake fetal ultrasounds (November 01, 2010)". Modern Medicine Network. Archived from the original on 2017-09-11. Retrieved 11 September 2017.
- Bricker, L; Garcia, J; Henderson, J; Mugford, M; Neilson, J; Roberts, T; Martin, MA (2000). "Ultrasound screening in pregnancy: A systematic review of the clinical effectiveness, cost-effectiveness and women's views". Health Technology Assessment. 4 (16): i–vi, 1–193. doi:10.3310/hta4160. PMID 11070816.
- Ang, E. S. B. C.; Gluncic, V.; Duque, A.; Schafer, M. E.; Rakic, P. (2006). "Prenatal exposure to ultrasound waves impacts neuronal migration in mice". Proceedings of the National Academy of Sciences. 103 (34): 12903–10. Bibcode:2006PNAS..10312903A. doi:10.1073/pnas.0605294103. PMC 1538990. PMID 16901978.[non-primary source needed]
- Kieler, Helle; Cnattingius, Sven; Haglund, Bengt; Palmgren, Juni; Axelsson, Ove (2001). "Sinistrality—a side-effect of prenatal sonography: A comparative study of young men". Epidemiology. 12 (6): 618–23. doi:10.1097/00001648-200111000-00007. PMID 11679787. S2CID 32614593.[non-primary source needed]
- Salvesen, K A; Vatten, L J; Eik-Nes, S H; Hugdahl, K; Bakketeig, L S (1993). "Routine ultrasonography in utero and subsequent handedness and neurological development". BMJ. 307 (6897): 159–64. doi:10.1136/bmj.307.6897.159. PMC 1678377. PMID 7688253.[non-primary source needed]
- Kieler, Helle; Axelsson, Ove; Haglund, Bengt; Nilsson, Staffan; Salvesen, Kjell Å. (1998). "Routine ultrasound screening in pregnancy and the children's subsequent handedness". Early Human Development. 50 (2): 233–45. doi:10.1016/S0378-3782(97)00097-2. PMID 9483394.[non-primary source needed]
- Heikkilä, K.; Vuoksimaa, E.; Oksava, K.; Saari-Kemppainen, A.; Iivanainen, M. (2011). "Handedness in the Helsinki Ultrasound Trial". Ultrasound in Obstetrics & Gynecology. 37 (6): 638–642. doi:10.1002/uog.8962. PMID 21305639. S2CID 23916007.[non-primary source needed]
- Salvesen, K. Å. (2011). "Ultrasound in pregnancy and non-right handedness: Meta-analysis of randomized trials". Ultrasound in Obstetrics & Gynecology. 38 (3): 267–271. doi:10.1002/uog.9055. PMID 21584892. S2CID 5135695.
- Legislation. ardms.org
- "Medical Technologist Certification & Degree Programs". MTS. Retrieved 2020-05-19.
- Deane, Collin (2002). "Safety of diagnostic ultrasound in fetal scanning". In Nicolaides, Kypros; Rizzo, Giuseppe; Hecker, Kurt; Ximenes, Renato (eds.). Doppler in Obstetrics.
- MTP and PCPNDT Initiatives Report Archived 2014-06-01 at the Wayback Machine Government of India (2011)
- IMPLEMENTATION OF THE PCPNDT ACT IN INDIA – Perspectives and Challenges. Public Health Foundation of India, Supported by United Nations FPA (2010)
- "THE PRE-NATAL DIAGNOSTIC TECHNIQUES (REGULATION AND PREVENTION OF MISUSE) ACT, 1994". mohfw.nic.in. 20 September 1994. Archived from the original on 24 January 2005.
- Siddharth, S.; Goyal, A. (2007). "The origin of echocardiography". Texas Heart Institute Journal. 34 (4): 431–438. PMC 2170493. PMID 18172524.
- Levine, H., III. (2010). Medical Imaging. Santa Barbara, California: ABC-CLIO, LLC., p. 62, describing earlier not completely successful attempt by the brothers to image a brain in 1937, which may be the same experiment
- "History of the AIUM". Archived from the original on November 3, 2005. Retrieved November 15, 2005.
- "The History of Ultrasound: A collection of recollections, articles, interviews and images". www.obgyn.net. Archived from the original on 5 August 2006. Retrieved 2006-05-11.
- Watts, G. (2009). "John Wild". BMJ. 339: b4428. doi:10.1136/bmj.b4428. S2CID 220114494.
- Australian Ultrasound Innovation
- Tilli Tansey; Daphne Christie, eds. (2000). Looking at the Unborn: Historical aspects of obstetric ultrasound. Wellcome Witnesses to Contemporary Medicine. History of Modern Biomedicine Research Group. ISBN 978-1-84129-011-9. Wikidata Q29581634.
- Looking at the Unborn: Historical aspects of obstetric ultrasound. History of Modern Biomedicine Research Group. 2000. ISBN 978-1-84129-011-9.
- Donald, Ian; MacVicar, J; Brown, T.G (1958). "Investigation of Abdominal Masses by Pulsed Ultrasound". The Lancet. 271 (7032): 1188–95. doi:10.1016/S0140-6736(58)91905-6. PMID 13550965.
- Edler, I.; Hertz, C. H. (2004). "The Use of Ultrasonic Reflectoscope for the Continuous Recording of the Movements of Heart Walls". Clinical Physiology and Functional Imaging. 24 (3): 118–36. doi:10.1111/j.1475-097X.2004.00539.x. PMID 15165281. S2CID 46092067.
- Woo, Joseph (2002). "A short History of the development of Ultrasound in Obstetrics and Gynecology". ob-ultrasound.net. Retrieved 2007-08-26.
- Zierler, R. Eugene (2002). "D. Eugene Strandness, Jr, MD, 1928–2002". Journal of Ultrasound. 21 (11): 1323–1325. doi:10.1067/mva.2002.123028.
- Medical Imaging Past Present and Future: 2 ARRT category A continuing education credits are available by way of an online post test at XRayCeRT.com. XRayCeRT. GGKEY:6WU7UCYWQS7.
- "Portable Ultrasound Equipment Market 2017 Global Leading Players Analysis & Industry Forecast to 2022". December 28, 2017. Archived from the original on December 30, 2017. Retrieved 29 December 2017.
- "Usono ProbeFix Introduces Continuous, Hands-Free Ultrasound to The World". November 16, 2017. Retrieved August 9, 2019.
|Wikimedia Commons has media related to Medical ultrasound.|