Orthotics (Greek: Ορθός, romanized: ortho, lit. 'to straighten, to align') is a medical specialty that focuses on the design and application of orthoses. An orthosis (plural: orthoses) is "an externally applied device used to influence the structural and functional characteristics of the neuromuscular and skeletal system".
Orthoses (orthotic devices) are classified into classes of four body areas according to the international classification system (ICS). There are the orthotics of the lower extremities (English: Classes of lower limb orthoses), orthotics of the upper extremities (English: Classes of upper limb orthoses), Orthoses for the trunk (English: Classes of spinal orthoses) and orthotics for the head (English : Classes of head orthoses).
In the area of the respective classes, Orthoses (orthotic devices) are grouped according to their function. There are paralysis orthoses, relief orthoses and soft braces.
Under the International Standard terminology, orthoses are classified by an acronym describing the anatomical joints which they contain. For example, a knee-ankle-foot orthosis (English abbreviation: KAFO for Knee-ankle-foot orthoses) spans the knee joint, the ankle and the foot. A spinal orthosis (English abbreviation: TLSO for Thorako-lumbo-sacral orthoses) affects the thoracic spine, the lumbar spine and the sacrum. Use of the International Standard is promoted to reduce the widespread variation in description of orthoses, which is often a barrier to interpretation of research studies.
The transition from an orthosis to a prosthesis can be fluid. An example of this is compensating for a leg length discrepancy, which is equivalent to replacing a missing part of a limb. Another example is the replacement of the forefoot after a forefoot amputation. This treatment is often made from a combination of a prosthesis to replace the forefoot and an orthosis to replace the lost muscular function (orthoprosthesis).
Prescription and manufacturing
An orthotist is the primary medical clinician responsible for the prescription, manufacture and management of orthoses. Orthoses are offered as custom-fabricated products, semi-finished products or finished products.
Custom-fabricated products are in the foreground of an optimal supply and are individually manufactured. If the physical examination of a patient is carried out precisely, the clinical picture often shows a combination of several functional deviations. Every single functional deviation can be slight or severe. The combination of the functional deviation and its characteristics lead to a detailed indication. A major advantage of custom-made products is that the various necessary orthotic functions when doing the configuration of the orthotics can be optimally matched to the determined functional deviations. Another advantage of custom-made products is that orthocis is made to fit the individual body shape of the patient. Custom-fabricated products were traditionally made by following a tracing of the extremity with measurements to assist in creating a well-fitted device. Subsequently, the advent of plastics and later even more modern materials such as carbon fiber composites and aramid fibers as a material of choice for construction necessitated the idea of creating a plaster of Paris mould of the body part in question. This method is still extensively used throughout the industry. By introducing composite materials made of carbon fiber materials and aramid fibers embedded in an epoxy resin matrix, the weight of modern orthoses is extremely reduced. With this technique, modern orthoses can achieve perfect stiffness in the areas where this is necessary (e.g. the connection between ankle and knee joint) and flexible areas where flexibility is required (e.g. in the area of the forefoot on the foot part of an orthosis).
Semi-finished products are used for fast supply in the case of diseases that occur frequently. They are manufactured industrially and in some cases can be adapted to the anatomical body conditions. Semi-finished products are also referred to as prefabricated products and custom fitted products, but in these cases it is not custom-fabricated.
Custom-fabricated products and Semi-finished products are used in long-term care and are manufactured or adapted by the orthotist or by trained orthopedic technicians according to the prescription. In many countries the physician or clinician defines the functional deviations in his prescription, e.g. paralysis (paresis) of the calf muscles (M. Triceps Surae) and derives the indication from this, e.g. orthotic to restore safety when standing and walking after a stroke. The orthotist creates another detailed physical examination and compares it with the prescription from the physician. The orthotist describes the configuration of the orthosis, which shows which orthotic functions are required to compensate for the functional deviation of the neuromuscular or skeletal system and which functional elements must be integrated into the orthosis for this. Ideally, the necessary orthotic functions and the functional elements to be integrated are discussed in an interdisciplinary team between physician, physical therapist, orthotist and patient.
Finished products are short-term orthoses or bandages for a limited duration of therapy and are manufactured industrially. Finished products are also referred to as off-the-shelf products.
The manufacture of modern orthoses requires that the orthotist acquire or have both manual skills in processing traditional and innovative materials and artistic skills in modeling body shapes. Orthotics also combines knowledge of anatomy and physiology, pathophysiology, biomechanics and engineering. Currently, CAD/CAM, CNC machines and 3D printing are involved in orthotic manufacture.
Lower limb orthoses
All orthoses that affect the foot, the ankle joint, the lower leg, the knee joint, the thigh or the hip joint belong to the category of orthoses for the lower extremities.
Paralysis orthoses are used both for paralyzes with complete functional failure of muscles or muscle groups, as well as for incomplete paralysis (paresis). They are intended to correct or influence functional limitations or to replace functions that have been lost as a result of the paralysis. Functional leg length differences caused by paralysis can be compensated for using the orthosis.
For the quality and function of a paralysis orthosis, it is of great importance that the orthotic shells are in total-contact fitting with the patient's leg due to an optimal fit. Therefore, a paralysis orthosis should be prescribed as a custom-made orthosis.
Reducing the weight of an orthosis makes a significant contribution to lowering the energy costs of walking for those affected, which is why the use of highly resilient and at the same time light materials such as carbon fiber, titanium and aluminum is indispensable for the manufacture of a custom-made orthosis.
The production of a custom-made orthosis also offers the advantage that orthotic joints can be integrated into the orthosis. By using orthotic joints, the dynamics of the orthotic can be matched exactly with the pivot points of the axes of movement of the anatomical joints of the lower extremity. Since the dynamics of the orthosis are realized via the orthotic joints, it is possible to manufacture the orthotic shells stable and torsion-resistant. As a result, the dynamics of the orthosis take place exactly where the movements are dictated by the anatomy in the skeletal system. This is necessary for the quality and function of the orthosis. The orthosis thus offers the necessary stability to regain the security that has been lost due to paralysis when standing and walking.
In addition, an orthosis can be individually configured through the use of orthosis joints. In this way, the function of the orthotic device can be optimally adjusted to any existing functional deviations that have resulted from the muscle weakness via the combination of the orthotic joints and the adjustability of the functional elements. The goal of high-quality orthotic fitting is to adapt the functional elements so precisely to the functional deviation that the orthosis provides the necessary support. At the same time, the orthotic device should restrict the dynamics of the lower extremities as little as possible through the adjustable dynamics of the orthotic joints in order to promote the remaining functionality of the muscles.[medical citation needed]
Determination of strength levels for physical examination
In the case of paralysis due to diseases or injuries to the spinal/peripheral nervous system, the strength levels of the six major muscle groups of the affected leg are first determined as part of the physical examination, in order to determine the necessary functions of an orthosis.
- The dorsiflexors move the foot through concentric muscle work around the axis of the ankle in the direction of dorsiflexion and control the plantar flexion through eccentric muscle work.
- The plantar flexors contribute significantly to being able to stand upright by actuating the forefoot lever and thereby increasing the standing area when standing. This group of muscles moves the foot in the direction of plantar flexion.
- The knee extensors extend the knee in the direction of the knee extension.
- The knee flexors bend the knee in the direction of the knee flexion.
- The hip flexors bend the hip joint in the direction of the hip flexion.
- The hip extensors stretch the hip joint in the direction of the hip extension and at the same time extend the knee in the direction of the knee extension.
A muscle function test according to Vladimir Janda is carried out to determine the strength levels. The degree of paralysis is given for each muscle group on a scale from 0 to 5, with the value 0 indicating complete paralysis (0%) and the value 5 indicating normal strength (100%). The values between 0 and 5 indicate a percentage reduction in muscle function. All strength levels below 5 are referred as muscle weakness.
The combination of strength levels of the muscle groups determines the type of orthosis (AFO or KAFO).
In addition, the strength levels of the muscle groups result in the necessary functional elements of the orthosis, which compensate for the restrictions caused by the reduced level of strength of the respective muscular functions.
Physical examination for paralysis due to diseases or injuries to the spinal cord/peripheral nervous system
Paralysis may be caused by diseases or injuries to the spinal or peripheral nervous system after spinal cord injury and also occur in spina bifida, poliomyelitis and Charcot-Marie-Tooth disease. In this group of paralyzes, the inclusion of the strength levels of the large muscle groups is of elementary importance in order to determine the necessary orthotic functions when configuring the orthosis.
Physical examination for paralysis due to diseases or injuries to the central nervous system
When determining the necessary functions of an orthosis, it makes sense to consider the group of paralyzes caused by diseases or injuries to the central nervous system separately from the group of paralyzes due to diseases or injuries to the spinal or peripheral nervous system. Incorrect motor impulses from the central nervous system often result in clearly visible deviations in the gait pattern. The necessary functions of an orthosis in this group of paralyzes can therefore only be determined to a limited extent by determining the muscle weakness in strength levels of the six major muscle groups. Even with results with high degrees of strength, disturbances of the gait pattern can be recognizable in these paralyzes due to the incorrect control of the central nervous system.
Cerebral palsy (CP) and traumatic brain injury
In patients with paralysis due to cerebral palsy (CP) and traumatic brain injury, but who are able to walk, the gait pattern is analyzed as part of the physical examination to determine the necessary functions of an orthosis. One way of assessing is the classification according to the "Amsterdam Gait Classification". According to this classification method, five gait types are described. To assess the gait pattern, the patient is viewed visually or via a video recording from the side of the leg to be assessed. At the point in time at which the leg to be viewed is in mid-stance and the leg not to be viewed in mid-swing, the knee angle and also the contact of the foot with the ground are assessed.
In gait type 1, the knee angle is normal and foot contact is complete. In gait type 2, the knee angle is hyperextended and the foot contact is complete. In gait type 3, the knee angle is hyperextended and foot contact is incomplete (only on the forefoot). In gait type 4, the knee angle is flexed and foot contact is incomplete (only on the forefoot). At gait 5, the knee angle is flexed and foot contact is complete.
Gait type 5 is also known crouch gait.
Patients with paralysis due to cerebral palsy or traumatic brain injury are usually treated with an ankle-foot orthosis (AFO). The functional elements to be used in the orthosis are the same as the functional elements of an AFO to compensate for paralysis of large muscle groups. However, it is important to understand that the muscle groups are not paralyzed, but are controlled by the brain with the wrong impulses. The compensatory gait is an unconscious reaction to the lack of security when standing or walking. The gait pattern usually worsens with increasing age. If the right functional elements are integrated into the orthosis, which both maintain physiological mobility and provide security when standing and walking, the necessary motor impulses can be created to create new cerebral connections. The goal of an orthotic fitting is the best possible approximation of the physiological gait pattern.
In the case of paralysis after a stroke, rapid care with an orthosis is sought. Often areas of the brain are affected that contain "programs" for controlling the musculoskeletal system. With the help of an orthosis, physiological standing and walking can be learned again, and late health consequences caused by a wrong gait pattern can be prevented. In order to consider the correct functional elements when configuring the orthosis, it is important to understand that the muscle groups are not paralyzed, but are controlled by the brain with wrong impulses, which is why a muscle function test according to Vladimir Janda can lead to incorrect results when assessing the ability to stand and walk.
An important basic requirement for regaining the ability to walk is that the patient trains early on to be able to stand on both legs safely and well balanced. An orthosis with functional elements to support balance and safety when standing and walking can already be integrated into the therapy concept to support the first standing exercises. This makes the work of mobilizing the patient at an early stage easier. If the right functional elements are integrated into the orthosis, which both maintain physiological mobility and provide security when standing and walking, the necessary motor impulses can be created to create new cerebral connections. Clinical studies confirm the importance of orthoses in stroke rehabilitation.
Patients with paralysis after a stroke are often treated with an ankle-foot orthosis (AFO).
After a stroke, it can happen that only the dorsiflexors are supplied with incorrect impulses from the central nervous system, which can lead to the risk of stumbling due to insufficient foot lifting when walking during swing phase. In these cases, an orthosis that only has functional elements to support the dorsiflexors can be helpful. Such an orthosis is also called drop foot orthosis. However, when configuring such a foot lifter orthosis, it makes sense to use adjustable functional elements for setting the resistance, which make it possible to adapt the passive lowering of the forefoot (plantar flexion) to the eccentric work of the dorsalflexors during loading response.
In many cases the muscle group of the plantar flexors is supplied with wrong impulses from the central nervous system, which leads to great uncertainty when standing and walking. The compensatory gait is an unconscious reaction to the lack of security when standing or walking. When configuring an orthosis, functional elements that can restore safety when standing and walking must be used in these cases. In such cases, a foot lifter orthosis is not suitable for restoring the lack of safety, since it only has functional elements that compensate for the functional deviations in the event of weakness of the dorsiflexors.
In patients with paralysis after stroke, but who are able to walk have the option of analyzing the gait pattern as part of the patient history in order to determine the optimal function of an orthosis. One way of assessing is the classification according to the "N.A.P. Gait Classification". N.A.P. is a physiotherapeutic treatment concept. According to this classification, four gait types are described. The gait pattern is assessed in the gait phase in which the leg to be viewed is in mid-stance phase and the leg not to be viewed is in mid-swing.
To assess the gait, in the first step, the patient is viewed visually or via a video recording from the side of the leg to be assessed. In gait type 1 the knee angle is hyperextended. In gait type 2 the knee angle is flexed.
The patient is then viewed from the front. If the forefoot is on the outer edge of the foot, which is accompanied by a varus position in the knee, the letter "a" is added to the gait. This foot position is called inversion. If the patient stands on the inner edge of the foot, which is associated with a valgus position in the knee, the letter "b" is added to the gait type. This foot position is called eversion.
The patients can be classified according to gait types 1a, 1b, 2a or 2b. The goal of orthotic fitting for patients who are able to walk is the best possible approximation of the physiological gait pattern.
Multiple sclerosis (MS)
In the case of paralysis due to multiple sclerosis, the degree of strength of the six major muscle groups of the affected leg should be determined as part of the physical examination, just as in the case of diseases or injuries to the spinal/peripheral nervous system, in order to determine the necessary functions of an orthosis. However, patients with multiple sclerosis may experience muscular or cognitive fatigue beyond the physiological level. The fatigue can be more or less pronounced and, depending on the severity, lead to considerable restrictions in everyday life. Persistent stress (e.g. walking) causes a deterioration in muscle function and has a significant effect on the spatial and temporal parameters when walking, for example by significantly reducing the cadence and walking speed. Fatigue can be measured as muscle weakness. As part of the patient's medical history when determining the strength levels of the six major muscle groups, fatigue can be taken into account by using a standardized walking test. The six-minute walk test is suitable for this. The muscle function test according to Vladimir Janda is carried out in combination with the six-minute walk test in the following steps:
- first muscle function test (without muscular fatigue)
- six-minute walk test directly followed by
- second muscle function test (with muscular fatigue)
This sequence of muscle function test and -minute walk test is used to check whether a controlled muscular fatigue can be induced. If the test reveals that there is muscular fatigue, the strength levels should be included in the planning of an orthosis, taking into account the measured fatigue when determining the functional elements.
Functional deviations in the case of paralysis of large muscle groups
Dorsiflexors – weakness of the dorsiflexors results in a so-called drop foot. The patient's foot can only be insufficiently lifted when walking during the swing phase, since the necessary concentric work of the dorsiflexors can not be activated. There is a risk of stumbling. In addition, the patient cannot influence the shock absorption when walking (gait phase, loading response), as the eccentric work of the dorsiflexors is limited. After Initial heel contact the forefoot slaps too quickly on the floor via the heel rocker, which creates an audible noise or the foot does touch the floor with forefoot first, which disrupts gait development.: 178–181 : 44–45, 50–54 and 126 
Plantar flexors – If the plantar flexors are weak, the muscles of the forefoot lever are only inadequately activated or not activated at all. The patient has no balance when standing and has to support himself with aids such as crutches. There is a lost of energy during walking. The forefoot lever required for energy-saving walking in the gait phases from mid-stance to pre-swing cannot be activated by the plantar flexors. This leads to excessive dorsiflexion in the ankle joint in terminal stance. The center of gravity of the body lowers towards the end of the stance phase and the knee of the contralateral leg is flexed excessively. With each step, the center of gravity must be raised above the leg with the excessively flexed knee by straightening it. Since the plantar flexors have their origin above the knee joint, they also have a knee-extension effect in the stance phase.: 177–210 >: 72 
Knee extensors – if the knee extensors are weak, there is an increased risk of falling. The physiological knee flexion is only inadequately or not controlled by the knee extensors when walking between loading response to the mid-stance. To control the knee, the patient develops compensatory mechanisms that lead to an incorrect gait pattern. That leads for example in the initial contact with the forefoot and not with the heel takes place in order to prevent the knee-flexing effect of the heel rocker. Another way to compensate for weak knee extensors is to exaggerate the activation of the plantar flexors, which leads into hyperextension of the knee.: 222, 226 : 132, 143, 148–149 
Functional elements for correction of functional deviations in large muscle groups
The functional elements of an orthosis ensure the flexion and extension movements of the ankle joint, the knee joint and the hip joint. They correct and control the movements and secure the joints against undesired incorrect movements, e.g. to avoid falls when standing or walking.
Functional deviations of the dorsiflexors – if the dorsiflexors are weak, an orthosis should lift the forefoot during the swing phase in order to reduce the risk of the patient stumbling. In addition, initial contact with the heel should be achieved by lifting the foot through the orthosis. Dynamic functional elements, in which the resistance of the plantar flexion can be adjusted, should take over the control of the rapid drop of the forefoot. They should be able to be adapted to the functional deviation of the dorsiflexors in order to correct the shock absorption via the heel rocker lever of the orthosis in loading response, without blocking the plantar flexion. Static functional elements that block the plantar flexion of the ankle joint lead to excessive flexion in knee and hip.: 105 : 134  An orthosis that has only one functional element for lifting the forefoot in order to compensate for a weakness in the dorsiflexors is also known as a drop foot orthosis. If other muscle groups, such as the plantar flexors, are weak, additional functional elements must be taken into account. An AFO of the drop foot orthosis type is therefore not suitable for the care of patients with weakness in other muscle groups.
Functional deviations of the plantar flexors – in order to compensate for a weakness of the plantar flexors, the orthosis has to transfer great forces that the strong muscle group of the plantar flexors would otherwise take over. The forces in the orthosis are transmitted in a similar way to a ski boot during downhill skiing via the functional elements of the foot part, ankle joint and lower leg shell. Dynamic functional elements should preferably be used in the ankle joint in order to secure the dorsiflexion. Static functional elements would completely block the dorsiflexion. A completely blocked dorsiflexion would have to be compensated by compensatory movements in the upper body, which would result in an increasing of energy cost when walking. The resistance of the functional element to protect against unwanted dorsiflexion should be able to be adapted to the weakness of the plantar flexors. In the case of very weak plantar flexors, the resistance of the functional element to secure against undesired dorsiflexion must be very high in order to be able to compensate for the functional deviations of the plantar flexors. Adjustable functional elements of an orthosis allow an exact adjustment of the resistance to the weakness of the muscle and scientific studies have come to the recommendation that the resistance of the orthosis should be adjustable in patients with paralysis or weakness of the plantar flexors.
Functional deviations of knee extensors and hip extensors – in the case of weak knee or hip extensors, the orthosis must take over the stability and stance phase control when walking. Depending on the weakness of these two muscle groups, different knee-securing functional elements are integrated into the orthosis. In order to compensate for functional deviations with slightly weakness of these muscle groups, free moving mechanical knee joints with a posterior shift of the mechanical pivot point behind the anatomical knee pivot point can be sufficient. In the case of significant weakness, the knee flexion effect when walking must be controlled by functional elements that mechanically secure the knee joint against unwanted knee flexion in the early stance phases between loading response and mid stance. Stance phase control knee joints can be used here. These lock the knee joint in the early stance phases and release the knee joint for knee flexion during the swing phase. With stance phase control knee joints, a natural gait pattern can be achieved despite mechanical securing against unwanted knee flexion. In these cases, locked knee joints are often used, which have a good safety function, but do not allow knee flexion when walking during swing phase. The knee joint remains mechanically locked during the swing phase. Patients with locked knee joints have to manage the swing phase with stiff leg. This only works if the patient develops compensatory mechanisms, e.g. by raising the body's center of gravity in the swing phase (Duchenne limping) or by swinging the orthotic leg to the side (circumduction). Stance phase control knee joints and locked joints can be mechanically "unlocked" so that the knee joint can be flexed to sit down.
Ankle–foot orthosis (AFO) in the field of paralysis orthoses
AFO is the abbreviation for ankle-foot orthoses; English name for an orthosis that spans the ankle and foot. In the treatment of paralyzed patients, an AFO is mainly used when there is a weakness of the dorsiflexors or plantar flexors.
Through the use of modern materials such as carbon fibers and aramid fibers and the new knowledge about processing these materials in composite fiber materials, the weight of orthotics has been extremely reduced compared to previous techniques. Taking into account the weight reduction, it were these materials and technologies that created the possibility of making special areas of an orthosis so rigid that the forces of the weakened muscles can actually be taken over by the AFO, e.g. the connection from the ankle joint to the frontal contact surface on the shin. At the same time, the areas in which flexibility is required can be produced very flexibly, e.g. the flexible part of the forefoot.
- Despite the necessary rigidity, the orthoses should not block the mobility of the ankle.
- Despite the necessary rigidity, the orthoses should not block the functionality of the muscles, but rather promote it.
- Despite the necessary rigidity, contractures and spasticity should not be stimulated.
Since several years it has been possible to combine the required rigidity of the orthotic shells with simultaneous dynamics in the ankle.
Different functional elements to compensate for a weakness of the dorsiflexors or a weakness of the plantar flexors can be integrated into the ankle joint of the orthosis depending on the combination of the degree of paralysis of the two muscle groups. In case of weakness of both muscle groups, both functional elements should be integrated in one orthotic joint. The necessary dynamics and the resistance to movements in the ankle are specifically adapted via adjustable functional elements in the ankle joint of the orthosis. In this way, the orthosis can compensate for muscle weaknesses in order to provide safety when standing and walking and at the same time allow as much mobility as possible. For example, adjustable spring units with pre-compression can enable an exact adaptation of the static basic resistance and the dynamic movement resistance to the measured degree of muscle weakness. Studies show the positive effects of these new technologies. It is of great advantage if the resistances for these two functional elements can be set separately.
An ankle joint based on new technology is the connection between the foot shell and the lower leg shell and at the same time contains all the necessary adjustable functional elements of an AFO. An AFO based on this can compensate for the functional deviations of the muscle groups mentioned. For this, the configuration of the AFO must be optimally matched to the patient through different variants with regard to the stiffness of the foot shell, different variants of the functional elements of a dynamic ankle joint and the different variants in the shape of the lower leg shell.
An AFO with functional elements to compensate for a weakness of the plantar flexors can also be used for slight weakness of the knee-securing muscle groups, the knee extensors and the hip extensors.
An AFO that has only one functional element for lifting the forefoot in order to compensate for a weakness in the dorsiflexors is also known as a drop foot orthosis. If other muscle groups, such as the plantar flexors, are weak, additional functional elements must be taken into account. An AFO of the drop foot orthosis type is therefore not suitable for the care of patients with weakness in other muscle groups.
Before these new technologies were available, there was a standard that the International Committee of the Red Cross published in its 2006 Manufacturing Guidelines for Ankle-Foot Orthoses. At that time, the aim was already to offer people with disabilities worldwide standardized processes for the production of high-quality, modern, durable and economical devices.
Because the new technologies are still not widely used, AFOs are often still made from polypropylene-based plastic, mostly in the shape of an "L" with the upright part behind the calf and the lower part under the foot. The continuous "L" shape of these constructions, however, only offers the rigidity that can be produced with these materials. Such constructions made of polypropylene are still called "DAFO (dynamic ankle-foot orthosis)", "SAFO (solid ankle-foot orthosis)" or "Hinged AFO". Either they are not stable enough to transfer the high forces required to balance the weak plantar flexors when standing and walking (DAFO) or they block the mobility of the ankle joint (SAFO). A "Hinged AFO" at that time, only allow for the compensation of that kind of muscular weakness that could be achieved with the orthotic joints available at that time. In this technology, for example, it is still common to block plantar flexion, as the orthotic joints available at the time cannot simultaneously transmit the large forces that are required to compensate for muscle deviations and at the same time offer the necessary dynamics. While there was this multitude of AFOs in clinical practice, which differed in their design, studies have already established that there was a clear lack of details regarding the design and the material and a new standardization of the terminology was called for. With a focus on the care of children with cerebral palsy (CP), there was already a recommendation from clinical practice in the context of the manufacture of orthotics made of polypropylene and their multitude of possible designs that the potential for improving the gait pattern through specifically adapted orthotics through further studies to investigate. The integration of orthotic joints with modern functional elements in the old production technology with polypropylene, on the other hand, is unusual because the orthotic shells made of polypropylene could not transfer the high forces under the boundary condition of an acceptable weight or would be too soft.
Unfortunately, today's terminologies were determined on the basis of the technologies available until then and therefore now require a particularly high level of explanation.
The International Committee of the Red Cross published its manufacturing guidelines for ankle–foot orthoses in 2006. Its intent is to provide standardized procedures for the manufacture of high-quality modern, durable and economical devices to people with disabilities throughout the world. Because of the studies already mentioned above which recognize the new technologies available, the main types mentioned are in need of revision today.
|Designation of the orthosis according to one function: S for solid
plus the body parts included in the orthosis fitting: ankle and foot, English abbreviation: AFO for ankle-foot orthoses
|Designation of the orthosis according to one function: D for dynamic
plus the body parts included in the orthosis fitting: ankle and foot, English abbreviation: AFO for ankle-foot orthoses
|Designation of the orthosis according to one function: Hinged
plus the body parts included in the orthosis fitting: ankle and foot, English abbreviation: AFO for ankle-foot orthoses
"Hinged" simply means a flexible connection between the two parts of the orthosis. The joint itself does not offer any further functional elements.
|Designation of the orthosis according to one function:
"Posterior Leaf Spring"
Spring made from flexible material behind (posterior) the ankle
A DAFO often also known as "Posterior Leaf Spring"
|Designation of the orthosis according to one function:
FR for Floor reaction
Designation is misleading as other orthoses also have this function
|Designation of the orthosis according to the body parts included in the orthosis fitting: ankle and foot, English abbreviation: AFO for ankle-foot orthoses.
Plus further descriptions, such as: - lightweight carbon fiber ventral shell with torsionally rigid reinforcement to focus the dynamics on the ankle joint
- dynamic ankle joint with precompressed spring elements to control plantarflexion and dorsiflexion
|Designation given by the Red Cross in 2006:
|Designation given by the Red Cross in 2006:
|Designation given by the Red Cross in 2006:
AFO with Tamarack Flexure JointTM
|Not mentioned by the Red Cross in 2006||Not mentioned by the Red Cross in 2006||Not mentioned by the Red Cross in 2006|
||Depending on which functional elements are integrated in the ankle joint used, such an orthosis can enable the following functions:
Knee-ankle-foot orthosis (KAFO) in the field of paralysis orthoses
KAFO is the abbreviation for ankle-foot orthoses; English name for an orthosis that spans the knee, the ankle and the foot. In the treatment of paralyzed patients, a KAFO is used when there is a weakness of the knee extensors or hip extensors. Motion at all three of these lower limb areas is affected by a KAFO and can include stopping motion, limiting motion, or assisting motion in any or all of the three planes of motion in a human joint: sagittal, coronal, and axial. Mechanical hinges, as well as electrically controlled hinges have been used. Various materials for fabrication of a KAFO include but are not limited to metals, plastics, fabrics, and leather. Conditions that might benefit from the use of a KAFO include paralysis, joint laxity or arthritis, fracture, and others. Although not as widely used as knee orthoses, KAFOs can make a real difference in the life of a paralyzed person, helping them to walk therapeutically or, in the case of polio patients, on a community level. These devices are expensive and require maintenance. Some research is being done to enhance the design; even NASA helped spearhead the development of a special knee joint for KAFOs.
Hip-knee-ankle-foot orthosis (HKAFO) in the field of paralysis orthoses
HKAFO is the abbreviation for ankle-foot orthoses; English name for an orthosis that spans the hip, the knee, the ankle and the foot. In the treatment of paralyzed patients, a HKAFO is used when there is a weakness of the pelvic stabilizing trunk muscles.
Relief orthoses are used both in degeneration and after injuries to joints. These includes torn ligaments and wear and tear of joints. Relief orthoses are also used after operations such as a complete replacement of a joint or operations on the joint structure or other operations on bony, muscular structures or operations on the joint ligaments.
Relief orthosis may also be used to:
- Control, guide, limit and/or immobilize an extremity, joint or body segment for a particular reason
- Restrict movement in a given direction
- Assist movement generally
- Reduce weight-bearing forces for a particular purpose
- Aid rehabilitation from fractures after the removal of a cast
- Otherwise correct the shape and/or function of the body, to provide easier movement capability or reduce pain
Ulcer healing orthosis (UHO)
A custom-made ankle/foot orthosis for the treatment of patients having plantar ulcers is disclosed, which comprises a rigid L-shaped support member and a rigid anterior support shell hingedly articulated to the L-shaped support member. The plantar portion of the L-shaped member further comprises at least one ulcer-protecting hollow spatially located for fitted placement in inferior adjacency to a user's plantar ulcer, thus allowing the user to transfer the user's weight away from the plantar ulcer and facilitating plantar ulcer treatment. The anterior support shell is designed for lateral hinged attachment to the L-shaped member to take advantage of medial tibial flare structure for enhancing the weight-bearing properties of the disclosed orthosis. A flexible, polyethylene hinge member hingedly attaches the anterior support shell to the L-shaped member and securing straps securely attach the anterior support shell in fixed, weight-bearing relation about the proximal, anterior portion of the user's lower leg.
Foot orthoses (FO)
Foot orthoses (commonly called orthotics) are devices inserted into shoes to provide support for the foot by redistributing ground reaction forces acting on the foot joints while standing, walking or running. They may be either pre-moulded (also called pre-fabricated) or custom made according to a cast or impression of the foot. A great body of information exists within the orthotic literature describing their medical use for people with foot problems as well as the impact orthotics can have on foot, knee, hip, and spine deformities. They are used by everyone from athletes to the elderly to accommodate biomechanical deformities and a variety of soft tissue conditions. Foot orthoses are effective at reducing pain for people with painful high-arched feet, and may be effective for people with rheumatoid arthritis, plantar fasciitis, First metatarsophalangeal (MTP) joint pain or hallux valgus (bunions). For children with juvenile idiopathic arthritis (JIA) custom-made and pre-fabricated foot orthoses may also reduce foot pain. Foot orthoses may also be used in conjunction with properly fitted orthopaedic footwear in the prevention of foot ulcers in the at-risk diabetic foot. A real-time weight bearing orthotic can be created using a neutral position casting device and the Vertical Foot Alignment System VFAS.
Ankle–foot orthosis (AFO) in the field of relief orthoses
An AFO is also used to immobilize the ankle and lower leg in the presence of arthritis or fracture.
Ankle–foot orthoses are the most commonly used orthoses, making up about 26% of all orthoses provided in the United States. According to a review of Medicare payment data from 2001 to 2006, the base cost of an AFO was about $500 to $700.
Knee orthosis (KO) in the field of relief orthoses
A knee orthosis (KO) or knee brace is a brace that extends above and below the knee joint and is generally worn to support or align the knee. In the case of diseases causing neurological or muscular impairment of muscles surrounding the knee, a KO can prevent flexion or extension instability of the knee. In the case of conditions affecting the ligaments or cartilage of the knee, a KO can provide stabilization to the knee by replacing the function of these injured or damaged parts. For instance, knee braces can be used to relieve pressure from the part of the knee joint affected by diseases such as arthritis or osteoarthritis by realigning the knee joint into valgus or varus. In this way a KO may help reduce osteoarthritis pain, however, there is no clear evidence to advise people with osteoarthritis of the knee about the most effective orthosis to use or the best approach to rehabilitation. A knee brace is not meant to treat an injury or disease on its own, but is used as a component of treatment along with drugs, physical therapy and possibly surgery. When used properly, a knee brace may help an individual to stay active by enhancing the position and movement of the knee or reducing pain.
Prophylactic, functional and rehabilitation braces
Prophylactic braces are used primarily by athletes participating in contact sports. Evidence about prophylactic knee braces, the ones football linemen wear that are often rigid with a knee hinge, indicates they are ineffective in reducing anterior cruciate ligament tears, but may be helpful in resisting medial and lateral collateral ligament tears.
Functional braces are designed for use by people who have already experienced a knee injury and need support to recover from it. They are also indicated to help people who are suffering from pain associated with arthritis. They are intended to reduce the rotation of the knee and support stability. They reduce the chance of hyperextension, and increase the agility and strength of the knee. The majority of these are made of elastic. They are the least expensive of all braces and are easily found in a variety of sizes.
Rehabilitation braces are used to limit the movement of the knee in both medial and lateral directions- these braces often have an adjustable range of motion stop potential for limiting flexion and extension following ACL reconstruction. They are primarily used after injury or surgery to immobilize the leg. They are larger in size than other braces, due to their function.
A soft brace is sometimes also called soft support or a bandage. Bandages, which belong to the field of orthoses, are so-called support bandages, which are supposed to protect the joints from excessive loads. Soft braces are also classified according to regions of the body. In sport, bandages are used to protect bones and joints. One of the purposes of these braces is injury protection. They mostly consist of textiles, some of which have supportive elements. The supporting functions are low compared to paralysis and relief orthoses. Bandages should also achieve proprioceptive effects. Equally, orthoses are sometimes used prophylactically or to optimise performance in sport. At present, the scientific literature does not provide sufficient high quality research to allow strong conclusions on their effectiveness and cost-effectiveness.
Upper limb orthoses
Upper-limb (or upper extremity) orthoses are mechanical or electromechanical devices applied externally to the arm or segments thereof in order to restore or improve function or structural characteristics of the arm segments encumbered by the device. In general, musculoskeletal problems that may be alleviated by the use of upper limb orthoses include those resulting from trauma or disease (arthritis for example). They may also be beneficial in aiding individuals who have suffered a neurological impairment such as stroke, spinal cord injury, or peripheral neuropathy. Disease is the standard respiratory rate.
Types of upper-limb orthoses
- Upper-limb orthoses
- Clavicular and shoulder orthoses
- Arm orthoses
- Functional arm orthoses
- Elbow orthoses
- Forearm-wrist orthoses
- Forearm-wrist-thumb orthoses
- Forearm-wrist-hand orthoses
- Hand orthoses
- Upper-extremity orthoses (with special functions)
Scoliosis, a condition describing an abnormal curvature of the spine, may in certain cases be treated with spinal orthoses, such as the Milwaukee brace, the Boston brace, Charleston bending brace, and Providence brace. As this condition develops most commonly in adolescent females who are undergoing their pubertal growth spurt, compliance with wearing is these orthoses is hampered by the concern these individuals have about changes in appearance and restriction caused by wearing these orthoses. Spinal orthoses may also be used in the treatment of spinal fractures.
A Jewett brace, for instance, may be used to facilitate healing of an anterior wedge fracture involving the T10 to L3 vertebrae. A body jacket may be used to stabilize more involved fractures of the spine. The halo brace is a cervical thoracic orthosis used to immobilize the cervical spine, usually following fracture. The halo brace allows the least cervical motion of all cervical orthoses currently in use; it was first developed by Vernon L. Nickel at Rancho Los Amigos National Rehabilitation Center in 1955.
Orthoses for the head
Helmets are an example of orthoses for the head.
Orthotists are healthcare professionals who specialize in the provision of orthoses. In the United States, orthotists work by prescription from a licensed healthcare provider. Physical therapists are not legally authorized to prescribe orthoses in the U.S. In the U.K., orthotists will often accept open referrals for orthotic assessment without a specific prescription from doctors or other healthcare professionals.
- "Prosthetics and orthotics". iso.org. International Organization for Standardization. Retrieved 11 August 2021.
- Ridgewell E, Dobson F, Bach T, Baker R (June 2010). "A systematic review to determine best practice reporting guidelines for AFO interventions in studies involving children with cerebral palsy". Prosthetics and Orthotics International. 34 (2): 129–45. doi:10.3109/03093641003674288. PMID 20384548.
- Fisk JR, DeMuth S, Campbell J, DiBello T, Esquenazi A, Lin RS, et al. (February 2016). "Suggested Guidelines for the Prescription of Orthotic Services, Device Delivery, Education, and Follow-up Care: A Multidisciplinary White Paper". Military Medicine. 181 (2 Suppl): 11–7. doi:10.7205/MILMED-D-15-00542. PMID 26835739.
- Gatt, Alfred; Grech, Mark; Chockalingam, Nachiappan; Formosa, Cynthia (17 May 2017). "A Preliminary Study on the Effect of Computer-Aided Designed and Manufactured Orthoses on Chronic Plantar Heel Pain". Foot & Ankle Specialist. 11 (2): 112–116. doi:10.1177/1938640017709906. ISSN 1938-6400. PMID 28513217. S2CID 4298371.
- Brehm, MA; Beelen, A; Doorenbosch, CAM; Harlaar, J; Nollet, F (2007). "Effect of carbon-composite knee-ankle-foot orthoses on walking efficiency and gait in former polio patients". Journal of Rehabilitation Medicine. 39 (8): 651–657. doi:10.2340/16501977-0110. ISSN 0001-5555. PMID 17896058.
- Kobayashi T, Leung AK, Akazawa Y, Hutchins SW (March 2013). "The effect of varying the plantarflexion resistance of an ankle-foot orthosis on knee joint kinematics in patients with stroke". Gait & Posture. 37 (3): 457–9. doi:10.1016/j.gaitpost.2012.07.028. hdl:10397/11188. PMID 22921491.
- Ploeger HE, Waterval NF, Nollet F, Bus SA, Brehm MA (7 August 2019). "Stiffness modification of two ankle-foot orthosis types to optimize gait in individuals with non-spastic calf muscle weakness – a proof-of-concept study". Journal of Foot and Ankle Research. 12 (1): 41. doi:10.1186/s13047-019-0348-8. PMC 6686412. PMID 31406508.
- Waterval, Niels F. J.; Nollet, Frans; Harlaar, Jaap; Brehm, Merel-Anne (17 October 2019). "Modifying ankle foot orthosis stiffness in patients with calf muscle weakness: gait responses on group and individual level". Journal of NeuroEngineering and Rehabilitation. 16 (1). doi:10.1186/s12984-019-0600-2. ISSN 1743-0003.
- Meyns P, Kerkum YL, Brehm MA, Becher JG, Buizer AI, Harlaar J (May 2020). "Ankle foot orthoses in cerebral palsy: Effects of ankle stiffness on trunk kinematics, gait stability and energy cost of walking". European Journal of Paediatric Neurology. 26: 68–74. doi:10.1016/j.ejpn.2020.02.009. PMID 32147412.
- Kerkum YL, Buizer AI, van den Noort JC, Becher JG, Harlaar J, Brehm MA (23 November 2015). "The Effects of Varying Ankle Foot Orthosis Stiffness on Gait in Children with Spastic Cerebral Palsy Who Walk with Excessive Knee Flexion". PLOS ONE. 10 (11): e0142878. doi:10.1371/journal.pone.0142878. PMC 4658111. PMID 26600039.
- Nollet F, Noppe CT (2008). Hsu JD, Michael J, Fisk J (eds.). Orthoses for persons with postpolio syndrome. Philadelphia. Mosby Elsevier. pp. 411–417. ISBN 978-0-323-03931-4.
- Janda V (2000). Manuelle Muskelfunktionsdiagnostik. ISBN 3-437-46430-2.
- Fatone S (2009). "Chapter 31: Orthotic Management in Stroke". In Stein J, Harvey RL, Macko RF, Winstein CJ, Zarowitz RD (eds.). Stroke Recovery & Rehabilitation. New York. Demos Medical. pp. 522–523. ISBN 978-1-933864-12-9.
- Rodda J, Graham HK (November 2001). "Classification of gait patterns in spastic hemiplegia and spastic diplegia: a basis for a management algorithm". European Journal of Neurology. 8 (Suppl 5): 98–108. doi:10.1046/j.1468-1331.2001.00042.x. PMID 11851738. S2CID 45860264.
- Grunt S. "Geh-Orthesen bei Kindern mit Cerebralparese". Pediatrica. 18: 30–34.
- Esquenazi A (2008). Hsu JD, Michael JW, Fisk JR (eds.). Assessment and orthotic management of gait dysfunction in individuals with brain injury. AAOS Atlas of Orthoses and Assistive Devices. Philadelphia. Mosby Elsevier. pp. 441–447. ISBN 978-0-323-03931-4.
- Horst R (2005). Motorisches Strategietraining und PNF. Georg Thieme Verlag. ISBN 978-3-13-151351-9.
- Kerkum YL, Harlaar J, Buizer AI, van den Noort JC, Becher JG, Brehm MA (May 2016). "An individual approach for optimizing ankle-foot orthoses to improve mobility in children with spastic cerebral palsy walking with excessive knee flexion". Gait & Posture. 46: 104–11. doi:10.1016/j.gaitpost.2016.03.001. PMID 27131186.
- Nudo RJ, Barbay S (2009). "The Mechanisms and Neurophysiology of Recovery from Stroke". In Stein J, Harvey RL, Macko RF, Winstein CJ, Zorowitz RD (eds.). Stroke Recovery & Rehabilitation. New York. Demos Medical. pp. 123–134. ISBN 978-1-933864-12-9.
- Corsten T (2010). Die neurologische Frührehabilitation am Beispiel Schlaganfall – Analysen zur Entwicklung einer Qualitätssicherung [Neurological early rehabilitation using the example of a stroke – analyzes for the development of quality assurance] (PDF) (PhD thesis) (in German). Universität Hamburg.
- Horst R (2011). N.A.P. – Therapieren in der Neuroorthopädie. Stuttgart New York: Renata Horst. pp. 12–15, 63, 66 and 77. ISBN 978-3-13-146881-9.
- Owen E (September 2010). "The importance of being earnest about shank and thigh kinematics especially when using ankle-foot orthoses". Prosthetics and Orthotics International. Prosthetics and Orthotics International. 34 (3): 254–69. doi:10.3109/03093646.2010.485597. PMID 20738230. S2CID 38130573.
- Bowers R (2004). "Report of a Consensus Conference on the Orthotic Management of Stroke Patients, Non-Articulated Ankle-Foot Ortheses" (PDF). International Society for Prosthetics and Orthotics: 87–94.
- Horst R (2011). N.A.P. – Therapieren in der Neuroorthopädie. Stuttgart New York: Renata Horst. ISBN 978-3-13-146881-9.
- Phan-Ba R, Calay P, Grodent P, Delrue G, Lommers E, Delvaux V, et al. (13 April 2012). "Motor fatigue measurement by distance-induced slow down of walking speed in multiple sclerosis". PLOS ONE. 7 (4): e34744. doi:10.1371/journal.pone.0034744. PMC 3326046. PMID 22514661.
- DeCeglie S, Dehner S, Ferro S, Lamb R, Tomaszewski L, Cohen ET (2016). Alterations in Temporal-Spatial Gait Parameters in People with Multiple Sclerosis–a Systematic Review. CMSC Annual Meeting.
- Kalron A (April 2015). "Association between perceived fatigue and gait parameters measured by an instrumented treadmill in people with multiple sclerosis: a cross-sectional study". Journal of Neuroengineering and Rehabilitation. 12: 34. doi:10.1186/s12984-015-0028-2. PMC 4403837. PMID 25885551.
- Leone C, Severijns D, Doležalová V, Baert I, Dalgas U, Romberg A, et al. (May 2016). "Prevalence of Walking-Related Motor Fatigue in Persons With Multiple Sclerosis: Decline in Walking Distance Induced by the 6-Minute Walk Test". Neurorehabilitation and Neural Repair. 30 (4): 373–83. doi:10.1177/1545968315597070. PMID 26216790. S2CID 35067172.
- Winter DA (2009). Biomechanics and Motor Control of Human Movements. Hoboken, New Jersey: David A. Winter. pp. 236–239. ISBN 978-0-470-39818-0.
- Perry J, Burnfield JM (2010). Gait Analysis Noraml and Pathological Function. Thorofare. ISBN 978-1-55642-766-4.
- Götz-Neumann K (2006). Gehen verstehen – Ganganalyse in der Physiotherapie. Stuttgart / New York. ISBN 978-3-13-132373-6.
- Meadows B, Bowers RJ, Owen E (12 July 2016) . Biomechanics of the hip, knee, and ankle. Musculoskeletal Key. John D. Hsu, John W. Michael, John R. Fisk. pp. 299–309. ISBN 978-0-323-03931-4. Retrieved 11 July 2021.
- Kerkum YL (2016). "The effect of ankle foot orthosis stiffness on trunk movement and walking energy cost in cerebral palsy". Gait & Posture. 49: 2. doi:10.1016/j.gaitpost.2016.07.070. ISSN 0966-6362.
- Meadows B, Bowers RJ, Owen E (2008). Hsu JD, Michael JW, Fisk JR (eds.). Biomechanics of the hip, knee and ankle. AAOS Atlas of Orthoses and Assistive Devices (in German) (4 ed.). Philadelphia: Mosby Elsevier. pp. 299-309. ISBN 978-0-323-03931-4.
- Michael JW (2008). Hsu JD, Michael JW, Fisk JR (eds.). Lower limb orthoses. AAOS Atlas of Orthoses and Assistive Devices (in German) (4 ed.). Philadelphia: Mosby Elsevier. pp. 343-355. ISBN 978-0-323-03931-4.
- Desloovere K, Molenaers G, Van Gestel L, Huenaerts C, Van Campenhout A, Callewaert B, et al. (October 2006). "How can push-off be preserved during use of an ankle foot orthosis in children with hemiplegia? A prospective controlled study". Gait & Posture. 24 (2): 142–51. doi:10.1016/j.gaitpost.2006.08.003. PMID 16934470.
- Waterval NF, Nollet F, Harlaar J, Brehm MA (October 2019). "Modifying ankle foot orthosis stiffness in patients with calf muscle weakness: gait responses on group and individual level". Journal of Neuroengineering and Rehabilitation. 16 (1): 120. doi:10.1186/s12984-019-0600-2. PMC 6798503. PMID 31623670.
- Novacheck TF (2008). Orthoses for cerebral palsy. AAOS Atlas of Orthoses and Assistive Devices. Philadelphia: John D. Hsu, John W. Michael, John R. Fisk. pp. 487–500. ISBN 978-0-323-03931-4.
- Muñoz S (2018). "The new generation of AFOs". The O&P EDGE. 11.
- Alnajjar, Fady; Zaier, Riadh; Khalid, Sumayya; Gochoo, Munkhjargal (28 December 2020). "Trends and Technologies in Rehabilitation of Foot Drop: A Systematic Review". Expert Review of Medical Devices. 18 (1): 31–46. doi:10.1080/17434440.2021.1857729. ISSN 1743-4440. PMID 33249938. S2CID 227234568.
- "ICRC AFO Manufacturing Guidelines" (PDF). icrc.org. Archived (PDF) from the original on 7 March 2016. Retrieved 20 March 2018.
- Eddison N, Mulholland M, Chockalingam N (August 2017). "Do research papers provide enough information on design and material used in ankle foot orthoses for children with cerebral palsy? A systematic review". Journal of Children's Orthopaedics. 11 (4): 263–271. doi:10.1302/1863-2548.11.160256. PMC 5584494. PMID 28904631.
- Eddison N, Chockalingam N (March 2021). "Ankle Foot Orthoses: Standardisation of terminology". Foot. 46: 101702. doi:10.1016/j.foot.2020.101702. PMID 33036836. S2CID 219517122.
- Eddison N, Chockalingam N (April 2013). "The effect of tuning ankle foot orthoses-footwear combination on the gait parameters of children with cerebral palsy". Prosthetics and Orthotics International. 37 (2): 95–107. doi:10.1177/0309364612450706. PMID 22833518. S2CID 29917264.
- International Organization for Standardization, Part 3: Terms relating to orthoses. "Prosthetics and orthotics". iso.org. Retrieved 15 July 2021.
- "ISO 8549-3:2020". International Organization for Standardization (ISO). September 2020.
Prosthetics and orthotics – Vocabulary – Part 3: Terms relating to orthoses
- Lima D (2008). Orthoses in total joint replacement. Philadelphia: John D. Hsu, John W. Michael, John R. Fisk. pp. 373–378. ISBN 978-0-323-03931-4.
- Wolters BW (2008). Hsu JD, Michael J, Fisk J (eds.). Knee orthoses for sports-related disorders. Philadelphia. pp. 379–389. ISBN 978-0-323-03931-4.
- US granted 6945946, Rooney JE, "Method and apparatus for the treatment of plantar ulcers and foot deformities", issued 20 Septembere 2005
- Welsh BJ, Redmond AC, Chockalingam N, Keenan AM (August 2010). "A case-series study to explore the efficacy of foot orthoses in treating first metatarsophalangeal joint pain". Journal of Foot and Ankle Research. 3 (1): 17. doi:10.1186/1757-1146-3-17. PMC 2939594. PMID 20799935.
- Hawke F, Burns J, Radford JA, du Toit V (July 2008). "Custom-made foot orthoses for the treatment of foot pain". The Cochrane Database of Systematic Reviews (3): CD006801. doi:10.1002/14651858.CD006801.pub2. hdl:1959.13/42937. PMID 18646168.
- Whiteside S, Allen MJ, Barringer WJ, Beiswenger WD, Brncick MD, Bulgarelli TD, et al. (January 2007). Practice analysis of certified practitioners in the disciplines of orthotics and prosthetics. Alexandria (VA): American Board for Certification in Orthotics, Prosthetics, and Pedorthics, Inc.
- Centers for Medicare and Medicaid Services, PSPS Files 2001–2006.
- "Knee braces for osteoarthritis". Mayo Clinic. Archived from the original on 28 February 2012.
- Duivenvoorden T, Brouwer RW, van Raaij TM, Verhagen AP, Verhaar JA, Bierma-Zeinstra SM (March 2015). "Braces and orthoses for treating osteoarthritis of the knee". The Cochrane Database of Systematic Reviews (3): CD004020. doi:10.1002/14651858.CD004020.pub3. PMC 7173742. PMID 25773267.
- Paluska SA, McKeag DB (January 2000). "Knee braces: current evidence and clinical recommendations for their use". American Family Physician. 61 (2): 411–8, 423–4. PMID 10670507. Archived from the original on 14 July 2014.
- Gravlee JR, Van Durme DJ (February 2007). "Braces and splints for musculoskeletal conditions". American Family Physician. 75 (3): 342–8. PMID 17304865. Archived from the original on 4 December 2010.
- Redford JB, Basmajian JV, Trautman P (1995). Orthotics: clinical practice and rehabilitation technology. New York: Churchill Livingstone. pp. 11–12.
- Healy A, Farmer S, Pandyan A, Chockalingam N (14 March 2018). "A systematic review of randomised controlled trials assessing effectiveness of prosthetic and orthotic interventions". PLOS ONE. 13 (3): e0192094. doi:10.1371/journal.pone.0192094. PMC 5851539. PMID 29538382.
- Lansang Jr RS (18 March 2009). "Upper Limb Orthotics". eMedicine from WebMD. Archived from the original on 25 September 2010. Retrieved 15 September 2010.
- Nickel VL, Perry J, Garrett A, Heppenstall M (October 1968). "The halo. A spinal skeletal traction fixation device". The Journal of Bone and Joint Surgery. American Volume. 50 (7): 1400–9. doi:10.2106/00004623-196850070-00009. PMID 5677293.[permanent dead link]
- "Standards of proficiency – Prosthetists / orthotists" (PDF). Health and Care Professions Council. London. August 2013. Archived from the original (PDF) on 6 October 2013. Retrieved 5 October 2013.